Detection and monitoring using high frequency electrogram analysis

ABSTRACT

An implantable device for analyzing a high frequency (HF) electrogram signal including an implantable electrode, a signal pickup configured to pick up an electrogram signal including a HF component, a signal filter connected to the signal pickup and configured to measure a HF component from the signal only during a specific portion of a cardiac cycle, and an analyzer for analyzing the HF component, wherein the signal pickup, the signal filter and the analyzer are included within an implantable container, and the analyzer is configured to analyze at least one time-varying parameter of the HF component, and the signal filter is configured to measure the signal by using a signal picked up from at least one electrode selected from a group consisting of (a) intracardiac, (b) subcutaneous, (c) a can of the implanted device, (d) a combination of two of the above. Related apparatus and methods are also described.

RELATED APPLICATIONS

This application is a Continuation In Part of U.S. patent applicationSer. No. 14/299,331 filed Jun. 9, 2014, which claims the benefit ofpriority under 35 USC 119(e) of U.S. Provisional Patent Application No.61/832,863 filed Jun. 9, 2013. The contents of the above Applicationsare all incorporated herein by reference.

FIELD AND BACKGROUND OF THE INVENTION

The present invention, in some embodiments thereof, relates to anapparatus and method for detecting myocardial ischemia using analysis ofhigh frequency components of an electrocardiogram and/or of a cardiacelectrogram, and, more particularly, but not exclusively, to animplantable such apparatus and method.

An electrocardiogram (ECG) is used to measure rate and regularity ofheartbeats, as well as a size and position of heart chambers, presenceof damage to the heart, and effects of drugs or devices used to regulatethe heart.

Usually two or more electrodes are used for electrocardiogram (ECG)measurement. The electrodes can be combined into a number of pairs.Output from a pair of electrodes is known as a lead.

An ECG is a common way to measure and diagnose abnormalities inelectrical activity of the cardiac muscle and abnormal rhythms of theheart, particularly abnormalities caused by damage to conductive tissuethat carries electrical signals, or abnormal rhythms caused byelectrolyte imbalances. In a condition of myocardial infarction (MI),the ECG can identify if the heart muscle has been damaged and sometimealso indicate the location of damage, though not all areas of the heartare covered.

A typical ECG device detects and amplifies tiny electrical changes on asubject's skin which are caused when a heart muscle depolarizes andsubsequently repolarizes during each heartbeat. At rest, each cardiacmuscle cell is negatively charged, causing a membrane potential acrossits cell membrane. A cell's activation phase commences withdepolarization, initiated by an influx of positive cations, Na+ andCa++, and decreasing the absolute value of the negative charge towardszero. The depolarization activates mechanical mechanisms in the cardiacmuscle cell which causes contraction in the cardiac muscle. During eachheart cycle, a healthy heart has an orderly progression as a wave ofdepolarization which is triggered by cells in the sinoatrial nodespreads out through the atrium, then passes through the atrioventricularnode and finally spreads over the ventricles. The progression isdetected as waveforms in the recorded potential difference (or voltage)between electrodes placed on either side of the heart and may bedisplayed as a graph either on screen or on paper. The produced signalreflects the electrical activity of the heart, and different leadsexpress more clearly different parts of the heart muscle.

A typical ECG trace of the cardiac cycle (heartbeat) consists of a Pwave, a QRS complex, a T wave, and a U wave which is normally visible in50% to 75% of ECG traces. A baseline voltage of the electrocardiogram isknown as the isoelectric line. Typically, the isoelectric line ismeasured as the portion of the ECG trace following the T wave andpreceding the next P wave.

A standard ECG traces usually filters out high frequency (HF)components, typically above 100 Hz. In some commercial implementations,lower thresholds such as 75 Hz or even 50 Hz are used for the low-passfiltering process. In general, the noise level is such that highfrequency components, above 150 Hz, which are typically measured inmicro-volts, are not reliably isolated from a single ECG trace andidentified or measured. In order to measure and process high frequencycomponents, one typically needs to use signal-to-noise enhancementschemes such as filtering and averaging.

An article by George B. Moody, Roger G. Mark, Andrea Zoccola and SaraMantero titled “Derivation of Respiratory Signals from Multi-lead ECGs”,published in Computers in Cardiology 1985, vol. 12, pp. 113-116,Washington, D.C.: IEEE Computer Society Press, describes asignal-processing technique which derives respiratory waveforms fromordinary ECGs, permitting detection of respiratory efforts.

Additional background art includes:

U.S. Pat. No. 8,706,201 to Beker et al.

U.S. Pat. No. 8,626,275 to Amit et al.

U.S. Pat. No. 8,538,510 to Toledo et al.

U.S. Pat. No. 7,539,535 to Schlegel et al.

U.S. Pat. No. 7,412,283 to Ginzburg et al.

U.S. Pat. No. 7,386,340 to Schlegel et al.

U.S. Pat. No. 7,239,988 to Hasson et al.

U.S. Pat. No. 7,151,957 to Beker et al.

U.S. Pat. No. 7,113,820 to Schlegel et al.

U.S. Pat. No. 6,600,949 to Turcott.

U.S. Pat. No. 6,128,526 to Stadler et al.

U.S. Pat. No. 5,954,664 to Seegobin.

U.S. Pat. No. 5,655,540 to Seegobin et al.

U.S. Pat. No. 5,404,877 to Nolan el al.

U.S. Pat. No. 5,348,020 to Hutson.

U.S. Pat. No. 5,117,833 to Albert et al.

U.S. Pat. No. 5,046,504 to Albert et al.

U.S. Pat. No. 4,422,459 to Simpson.

U.S. Patent Publication number 2005/0177049 to Hardahl et al.

U.S. Patent Publication number 2006/0074451 to Chen et al.

PCT Patent Application Publication WO 2005/104937.

The disclosures of all references mentioned above and throughout thepresent specification, as well as the disclosures of all referencesmentioned in those references, are hereby incorporated herein byreference.

SUMMARY OF THE INVENTION

An aspect of some embodiments of the invention relates to electrogramsignals gathered from implanted electrodes being stronger thanelectrocardiogram signals gathered from electrodes attached to asubject's skin.

An aspect of some embodiments of the invention relates to the stronger,and potentially higher signal-to-noise (S/N) ratio, electrogram signalsbeing synergistically conducive to analyzing high frequency (HF)electrogram signals, which are weaker, and potentially lower S/N ratio,when gathered from electrodes attached to a subject's skin. In thepresent specification and claims the term HF electrogram signals refersto components of an electrogram at frequencies above 100 Hz.

The term “electrocardiogram” is typically used in the art for a signalcollected by a sensor placed on a patient's skin. The term “electrogram”is typically used in the art for a signal collected by a sensor placedelsewhere, such as, by way of a non-limiting example, subcutaneously.The term “electrogram” is used throughout the present specification andclaims interchangeably with the term “electrocardiogram”.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering and/or analyzing electrogram signalsonly during a specific fraction of time, potentially lengtheningduration of operation between possible battery charging and/or batteryreplacement.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering and/or analyzing a high-frequencyportion of electrogram signals only during a specific fraction of time,potentially lengthening duration of operation between possible batterycharging and/or battery replacement.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering and/or analyzing a low-frequencyportion of electrogram signals only during a specific fraction of time,potentially lengthening duration of operation between possible batterycharging and/or battery replacing.

An aspect of some embodiments of the invention relates to electrogramsignals gathered from implanted electrodes enabling placing theelectrodes at locations physiologically different than only electrodesattached to a subject's skin

An aspect of some embodiments of the invention relates to electrogramsignals gathered from the can of an implanted apparatus, which saves ina total number of implanted electrodes.

An aspect of some embodiments of the invention relates to electrogramsignals gathered from electrodes located near to a known and/or to asuspected partial or complete occlusion in a blood vessel. Theelectrogram signal is optionally measured proximally and distally fromthe occlusion, and High frequency ECG values of the signal areoptionally compared.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing at least one electrogramsignal from an electrode located within a subject's body, (b) measuringthe electrogram signal at a high frequency during a specific segment ofa cardiac cycle, generating a HF electrogram signal, and (c) having acomputer measure at least one time-varying parameter of the HFelectrogram signal.

According to some embodiments of the invention, further including (d)having the computer detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter, and (e)having the computer generate an alert based, at least in part, on thedetection.

According to some embodiments of the invention, the measuring theelectrogram signal at a high frequency during a specific segment of acardiac cycle, generating a HF electrogram signal is performed such thata plurality of segments of the cardiac cycle are measured, and aplurality of the at least one time-varying parameter of the HFelectrogram signal are measured, for the plurality of segments of thecardiac cycle.

According to some embodiments of the invention, a duration of thespecific segment of a cardiac cycle is less than 40% of a duration of afull cardiac cycle.

According to some embodiments of the invention, the baseline value ofthe time-varying parameter is based on an average of the value of thetime-varying parameter belonging to a specific category.

According to some embodiments of the invention, further includingsimultaneously measuring at least two time-varying parameters of the HFelectrogram signal.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle includes a QRS complex.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle includes an interval selected from a group whichconsists of a P wave interval, and a T wave interval.

According to some embodiments of the invention, the measuring of theelectrogram signal at a high frequency during a specific segment of acardiac cycle includes not measuring the electrogram signal at a highfrequency during another segment of the cardiac cycle.

According to some embodiments of the invention, the computer detects achange in the time-varying parameter by comparing an HF electrogramsignal associated with a low heart rate to an HF electrogram signalassociated with a higher heart rate.

According to some embodiments of the invention, the higher heart rate isat least 20% higher than the low heart rate. This figure of 20% isoptionally a dynamically changeable parameter.

According to some embodiments of the invention the higher heart rate isoptionally set to be 40% higher, 60%, 100% and even 200% greater than aminimal heart rate.

According to some embodiments of the invention the higher heart rate isoptionally set in terms of a percentage of a maximal heart raterecommended, which is, by way of a non-limiting example, 220 minus apatient's age. In such embodiments values indicative of the higher heartrate are optionally in a range between 60-100% of the maximal heartrate.

According to some embodiments of the invention a value of a heart ratechange is optionally preset by a physician according to a patientphysical condition, such as age, sex, medical history, and historicalheart rate patterns.

In some embodiments a wireless communication unit is included in animplantable device, such that an operator, typically a physician, canchange parameters of the device using a programmer unit.

According to some embodiments of the invention a value of a heart ratechange is optionally learned by a learning mechanism which optimizes thevalue to reduce false positive detection of cardiac conditions. Thelearning is optionally done during an evaluation period in which thedevice learns a patient's signal patterns and sets the valueaccordingly.

In some embodiments, an evaluation period is included, when a patient isoptionally monitored by medical supervision. The evaluation period isoptionally a few days when the patient has an in-hospital evaluation, ora few weeks when the patient is monitored in an out-of-hospitalscenario. During this period, changes of the HF signal as a function ofHR are optionally evaluated, and optionally serve as a reference forfuture evaluation. The monitoring potentially provides an indication ifthere are ischemic episodes during the evaluation period. In some cases,during an evaluation period, no significant events occur, and in somecases there is a change of the HF signal as a function of HR even in nonischemic scenarios. Such changes are optionally taken into account toreduce false positive detection.

According to some embodiments of the invention, the sampling of theelectrogram signal at a high frequency includes sampling the electrogramsignal at a high frequency during a specific segment of a breathingcycle.

According to some embodiments of the invention, the electrogram signalis measured between an electrode which is placed in a heart chamber andan electrode which is placed outside the heart chamber.

According to some embodiments of the invention, the electrogram signalis measured between an electrode which is placed in a first heartchamber and an electrode which is placed in a second heart chamber.

According to some embodiments of the invention, further includingaligning and averaging a plurality of HF electrogram signals.

According to some embodiments of the invention, the aligning includessynchronization of HF electrogram signals based, at least in part, on apacing signal.

According to some embodiments of the invention, the comparison includescomparing a value of the time-varying parameter of the HF electrogramsignal and a baseline value of the time-varying parameter of the HFelectrogram signal at different instances of similar heart rate values.

According to some embodiments of the invention, the time-varyingparameter includes at least one selected from a group including an RMSlevel of the HF electrogram signal, a function of the RMS levels of theHF electrogram signal measured at a specific portion of a cardiac cycle,an envelope of the HF electrogram signal, a function of the envelope ofthe HF electrogram signal measured at a specific portion of a cardiaccycle, a width of the envelope of the HF electrogram signal, an area ofa reduced amplitude zone (RAZ) of the HF electrogram signal, and an areaof a RAZ in the envelope of the HF electrogram signal.

According to some embodiments of the invention, the alert is an alertindicating a condition selected from a group consisting of ischemia andother cardiac related events.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle includes a P wave interval, and further including (d)having the computer detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter, and (e)having the computer generate an alert indicating onset of atrialfibrillation based, at least in part, on the detection.

According to an aspect of some embodiments of the present inventionthere is provided IPG (implantable pulse generator) apparatus foranalyzing a high frequency (HF) electrogram signal including anelectrode for use inside a living body, a signal pickup configured topick up an electrogram signal including a high frequency (HF) component,a measurement unit for measuring a high frequency (HF) component fromthe electrogram signal during a specific segment of a cardiac cycle, andan analyzer for analyzing the HF component of the electrogram signal,wherein the signal pickup, the measurement unit and the analyzer areincluded within an implantable container, and the analyzer is configuredto measure at least one time-varying parameter of the HF electrogramsignal.

According to some embodiments of the invention, the analyzer isconfigured to detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter.

According to some embodiments of the invention, the analyzer is adaptedto receive a synchronization signal from a pacing unit in the apparatus.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing at least one electrogramsignal from an electrode located within a subject's body, (b) measuringthe electrogram signal at a high frequency during a specific segment ofa cardiac cycle, generating a HF electrogram signal, (c) having acomputer measure at least one time-varying parameter of the HFelectrogram signal, (d) having a computer detect a change in thetime-varying parameter in comparison to a baseline value of thetime-varying parameter, and (e) having the computer generate an alertbased, at least in part, on the detection.

According to some embodiments of the invention, the measuring theelectrogram signal at a high frequency during a specific segment of acardiac cycle, generating a HF electrogram signal is performed such thata plurality of segments of the cardiac cycle are measured, and aplurality of the at least one time-varying parameter of the HFelectrogram signal are measured, for the plurality of segments of thecardiac cycle.

According to some embodiments of the invention, a duration of thespecific segment of a cardiac cycle is less than 50% of a duration of afull cardiac cycle.

According to some embodiments of the invention, the alert is sent to acardiac pacing device.

According to some embodiments of the invention, the baseline value ofthe time-varying parameter is an average of the value of thetime-varying parameter measured previously under similar conditions.

According to some embodiments of the invention, further includingmeasuring at least two time-varying parameters of the HF electrogramsignal, having the computer compare the two or more time-varyingparameters of the HF electrogram signal, having the computer generate analert based, at least in part, on the comparison.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle is a QRS complex. According to some embodiments of theinvention, the specific segment of the cardiac cycle is selected from agroup which consists of a P wave interval, and a T wave interval.

According to some embodiments of the invention, the measuring of theelectrogram signal at a high frequency during a specific segment of acardiac cycle includes not measuring the electrogram signal at a highfrequency during another segment of the cardiac cycle.

According to some embodiments of the invention, the measuring of theelectrogram signal at a high frequency during a specific segment of acardiac cycle further includes measuring the electrogram signal at alower frequency during another segment of the cardiac cycle.

According to some embodiments of the invention, the high frequency isgreater than 100 Hz and the lower frequency is lower than 150 Hz.According to some embodiments of the invention, the high frequency isgreater than 150 Hz and the lower frequency is lower than 100 Hz.

According to some embodiments of the invention, detecting the segment ofthe cardiac cycle includes detecting atrial depolarization in theelectrogram signal.

According to some embodiments of the invention, the sampling of theelectrogram signal at a high frequency includes sampling the electrogramsignal at a high frequency during a specific segment of a breathingcycle.

According to some embodiments of the invention, detecting the segment ofthe breathing cycle includes measuring amplitude of a QRS complex of alow frequency electrogram.

According to some embodiments of the invention, detecting the segment ofthe breathing cycle includes measuring a duration of a cardiac cycle.

According to some embodiments of the invention, the electrogram signalis measured between two electrodes which are placed both in the sameheart chamber. According to some embodiments of the invention, theelectrogram signal is measured between an electrode which is placed in aheart chamber and an electrode which is placed outside the heartchamber. According to some embodiments of the invention, the electrogramsignal is measured between an electrode which is placed in a first heartchamber and an electrode which is placed in a second heart chamber.According to some embodiments of the invention, the electrogram signalis measured between an electrode which is placed touching a heart and anelectrode which is electrically coupled to a device can.

According to some embodiments of the invention, the electrogram signalis measured between two locations adjacent to a heart, opening at leasta 90 degree angle relative to a direction toward a center of mass of theheart.

According to some embodiments of the invention, the electrogram signalis measured between a first intracardiac electrode and a secondepicardiac electrode. According to some embodiments of the invention,the electrogram signal is measured between a first intracardiacelectrode and a second epicardiac electrode spaced apart to pick upsignals from a small part of the heart.

According to some embodiments of the invention, further includingaligning a plurality of HF electrogram signals to each other.

According to some embodiments of the invention, the aligning includesdetecting a time of onset of depolarization of the electrogram of singleelectrode placed in the heart.

According to some embodiments of the invention, the aligning includesdetecting a time of onset of depolarization of the electrogram of singleelectrode placed in the right cardiac atrium.

According to some embodiments of the invention, the comparison includescomparing a value of the time-varying parameter of the HF electrogramsignal and a baseline value of the time-varying parameter of the HFelectrogram signal at different instances of similar heart rate values.

According to some embodiments of the invention, the time-varyingparameter includes at least one selected from a group including an RMSlevel of the HF electrogram signal, a function of the RMS levels of theHF electrogram signal measured at a specific portion of a cardiac cycle,an envelope of the HF electrogram signal, a function of the envelope ofthe HF electrogram signal measured at a specific portion of a cardiaccycle, a width of the envelope of the HF electrogram signal, an area ofa reduced amplitude zone (RAZ) of the HF electrogram signal, and an areaof a RAZ in the envelope of the HF electrogram signal.

According to some embodiments of the invention, the alert includesdifferentiating between ventricular tachycardia and supraventriculartachycardia.

According to an aspect of some embodiments of the present inventionthere is provided an implantable device for analyzing a high frequency(HF) electrogram signal including an implantable electrode for useinside a living body, a signal pickup configured to pick up anelectrogram signal including a high frequency (HF) component, a signalfilter connected to the signal pickup and configured to measure a highfrequency (HF) component from the electrogram signal only during aspecific portion of a cardiac cycle, and an analyzer for analyzing theHF component of the electrogram signal, wherein the signal pickup, thesignal filter and the analyzer are included within an implantablecontainer, and the analyzer is configured to analyze at least onetime-varying parameter of the HF component of the electrogram signal,and the signal filter is configured to measure the electrogram signal byusing a signal picked up from at least one electrode selected from agroup consisting of (a) an intracardiac electrode, (b) a subcutaneouselectrode, (c) a can of the implanted device, (d) a combination of twoof the above.

According to some embodiments of the invention, the specific portion ofthe cardiac cycle includes at least part of a specific segment of thecardiac cycle, the specific segment of the cardiac cycle being one of agroup consisting of a P segment, a Q segment, a R segment, a S segment,a T segment, and a QRS complex segment.

According to some embodiments of the invention, the signal filter isarranged for measuring an electrogram signal only during a specificportion of a cardiac cycle.

According to some embodiments of the invention, the signal filter isarranged to start measuring the electrogram signal a specific period oftime following a synchronizing pacing signal.

According to some embodiments of the invention, the signal filter isarranged to start measuring the electrogram signal based, at least inpart, on detecting a specific point in a low-frequency electrogramsignal. According to some embodiments of the invention, the signalfilter is arranged to stop measuring the electrogram signal based, atleast in part, on detecting, in a low-frequency portion of theelectrogram signal, a specific segment of the cardiac cycle.

According to some embodiments of the invention, the analyzer isconfigured to detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle is a P segment, and the analyzer is configured toprovide indication of atrial arrhythmia, and further including a pacingunit for manipulating a pacing rate, based on the indication, toovercome the atrial arrhythmia.

According to some embodiments of the invention, the signal filter formeasuring a high frequency (HF) component from the electrogram signal isarranged to measure the electrogram signal at a frequency greater than500 Hz.

According to some embodiments of the invention, the pacing unit isarranged to manipulate the pacing rate to overcome the atrial arrhythmiaby increasing the pacing rate and subsequently decreasing the pacingrate.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle is a QRS complex, and the analyzer is configured toprovide indication of onset of an ischemic event, and further includinga pacing unit arranged to manipulate a pacing rate, based on theindication, to overcome the onset of the ischemic event by reducing thepacing rate.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing at least one electrogramsignal from an electrode located within a subject's body, (b) measuringthe electrogram signal at a high frequency only during a specificportion of a cardiac cycle, generating a HF electrogram signal for thespecific portion of the cardiac cycle, and (c) calculating at least onetime-varying parameter of the generated HF electrogram signal, whereinthe specific portion of the cardiac cycle includes at least part of aspecific segment of the cardiac cycle, the specific segment of thecardiac cycle being one of a group consisting of a P segment, a Qsegment, a R segment, a S segment, a T segment, and a QRS complexsegment.

According to some embodiments of the invention, at least 80% of thespecific segment of the cardiac cycle is within the specific portion ofthe cardiac cycle.

According to some embodiments of the invention, the measuring theelectrogram signal at a high frequency only during a specific segment ofa cardiac cycle includes measuring an electrogram signal at anyfrequency only during a specific segment of a cardiac cycle.

According to some embodiments of the invention, further including thecalculating includes calculating only when a correlation coefficientvalue of the generated HF electrogram signal to a template is largerthan a threshold value.

According to some embodiments of the invention, further including thecalculating includes calculating only when a noise level of thegenerated HF electrogram signal is smaller than a threshold value.

According to some embodiments of the invention, further includingaligning a plurality of HF electrogram signals based on synchronizationof the HF electrogram signals relative to a pacing signal.

According to some embodiments of the invention, further includingaligning a plurality of HF electrogram signals to a predefined template.According to some embodiments of the invention, the predefined templateis an electrogram segment from a prior heart beat. According to someembodiments of the invention, the predefined template is a curvecalculated by averaging electrogram segments from a plurality of priorheartbeats. According to some embodiments of the invention, thepredefined template is a curve calculated by fitting parameters to aninherent electrogram signal.

According to some embodiments of the invention, further including anelectrogram segment in the averaging of the electrogram segments onlywhen a noise level of the electrogram segment is smaller than athreshold value.

According to some embodiments of the invention, the providing at leastone electrogram signal from an electrode located within a subject's bodyincludes measuring an electrogram signal by using at least one electrodeselected from a group consisting of (a) an intracardiac electrode, (b) asubcutaneous electrode, (c) a can of an implanted device, (d) acombination of two of the above.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle is a P segment, and the analysis is used to providewarning of a condition selected from a group consisting of an irregularpropagation of an action potential in a cardiac atria, atrialtachycardia, atrial bradycardia, and atrial arrhythmia.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle is a P segment, and the analysis is used to providewarning of atrial arrhythmia, and further including manipulating apacing rate to overcome the atrial arrhythmia.

According to some embodiments of the invention, the manipulating thepacing rate to overcome the atrial arrhythmia includes increasing thepacing rate and gradually decreasing the pacing rate.

According to some embodiments of the invention, the specific segment ofthe cardiac cycle includes a QRS complex, and the analysis is used toprovide warning of onset of an ischemic event.

According to some embodiments of the invention, further includingreducing a pacing rate.

According to some embodiments of the invention, the analysis includesdetection of a reduction in amplitude of the HF electrogram signal.

According to some embodiments of the invention, the measuring theelectrogram signal at a high frequency includes measuring only a subband smaller than 500 Hz in a range of 100-2000 Hz.

According to some embodiments of the invention, the measuring only a subband includes measuring in a sub band range where the sub band range issmaller than a highest frequency of the sub band divided by 2.

According to some embodiments of the invention, the measuring only a subband includes measuring in a sub band range where the sub band range issmaller than twice a lowest frequency of the sub band.

According to some embodiments of the invention, the sampling of theelectrogram signal at a high frequency includes sampling the electrogramsignal at a high frequency during a specific segment of a breathingcycle.

According to some embodiments of the invention, further includingaligning and averaging a plurality of HF electrogram signals in whichthe aligning includes synchronization of HF electrogram signals based ona pacing signal.

According to some embodiments of the invention, further includingcomparing a value of the time-varying parameter of the HF electrogramsignal and a baseline value of the time-varying parameter of the HFelectrogram signal.

According to some embodiments of the invention, further includingcomparing a value of the time-varying parameter of the HF electrogramsignal and a prior value of the of the time-varying parameter of the HFelectrogram signal under same heart rate conditions.

According to some embodiments of the invention, the same conditions areselected from a group consisting of (a) same heart rate, (b) same heartrate increase, (c) same heart rate decrease, (d) same pattern of changeof heart rate.

According to some embodiments of the invention, further includingcomparing a current value of the time-varying parameter of the HFelectrogram signal and a prior value of the of the time-varyingparameter of the HF electrogram signal in which the prior value wasmeasured for a heart rate different by a pre set amount from a heartrate at which the prior value was measured.

According to an aspect of some embodiments of the present inventionthere is provided an implantable device for analyzing a high frequency(HF) electrogram signal including an implantable electrode for useinside a living body, a signal pickup configured to pick up anelectrogram signal including a high frequency (HF) component, ameasurement unit for measuring a high frequency (HF) component of theelectrogram signal only during a specific segment of a breathing cycle,and an analyzer for analyzing the HF component of the electrogramsignal, wherein the signal pickup, the measurement unit and the analyzerare included within an implantable container, the analyzer is configuredto analyze at least one time-varying parameter of the HF component ofthe electrogram signal, and the analyzer is configured to determine thespecific segment of the breathing cycle.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing at least one electrogramsignal from an electrode located within a subject's body, (b) measuringthe electrogram signal at a high frequency only during a specificsegment of a breathing cycle, generating a HF electrogram signal for thespecific segment of the breathing cycle, and (c) having a computermeasure at least one time-varying parameter of the HF electrogramsignal.

According to some embodiments of the invention, HF ECG parameters aremeasured only once during a breathing cycle.

According to some embodiments of the invention, the specific segment ofthe breathing cycle is measured by at least one motion sensors in animplanted device.

According to an aspect of some embodiments of the present inventionthere is provided IPG (implantable pulse generator) apparatus foranalyzing a high frequency (HF) electrogram signal including anelectrode for use inside a living body, a signal pickup configured topick up an electrogram signal including a high frequency (HF) component,a measurement unit for measuring a high frequency (HF) component fromthe electrogram signal during a specific segment of a cardiac cycle, andan analyzer for analyzing the HF component of the electrogram signal,wherein the signal pickup, the measurement unit and the analyzer areincluded within an implantable container, and the analyzer is configuredto measure at least one time-varying parameter of the HF electrogramsignal and to detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter.

According to some embodiments of the invention, the analyzer is adaptedto receive a synchronization signal from a pacing unit in the apparatus.

According to some embodiments of the invention, the analyzer is adaptedto receive a synchronization signal from a pacing unit in the apparatusand a detection of the specific segment of the cardiac cycle is based,at least in part, on the synchronization signal from the pacing unit.

According to some embodiments of the invention, the electrode includes abipolar electrode. According to some embodiments of the invention, theelectrode includes a monopolar electrode.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing a first electrogram signalfrom a first location of an intracoronary electrode adjacent to anocclusion of a coronary artery and proximal to the occlusion, (b)sampling the first electrogram signal at a high frequency, generating afirst high frequency (HF) electrogram signal, (c) providing a secondelectrogram signal from a second location of an intracoronary electrodeadjacent to the occlusion of the coronary artery and distal to theocclusion, (d) sampling the second electrogram signal at a highfrequency, generating a second high frequency (HF) electrogram signal,(e) measuring at least one time varying parameter of the first HFelectrogram signal and at least one time varying parameter of the secondHF electrogram signal, and (f) comparing, by a computer, the at leastone time varying parameter of the first HF electrogram signal and the atleast one time varying parameter of the second HF electrogram signal andproduce a result of the comparison.

According to some embodiments of the invention, the intracoronaryelectrode includes a monopolar electrode. According to some embodimentsof the invention, the intracoronary electrode includes a bipolarelectrode.

According to some embodiments of the invention, the occlusion of thecoronary artery is a suspected occlusion of the coronary artery.

According to some embodiments of the invention, the at least oneparameter of the first HF electrogram signal and the second HFelectrogram signal includes an

RMS value of the electrogram signals, and the comparison includes adifference between the RMS values at the first location and the secondlocation.

According to some embodiments of the invention, the comparison includesa function of numerical characteristics of an envelope of the first HFelectrogram signal and an envelope of the second HF electrogram signal.

According to some embodiments of the invention, the comparison includesa detection of a difference in ischemic condition between a first HFindex and a second HF index.

According to some embodiments of the invention, further includinganalyzing results from fractional flow reserve measurement (FFR).

According to some embodiments of the invention, further includingdetermining whether stent therapy is needed based on the result of thecomparison.

According to some embodiments of the invention, further includingpost-revascularization assessment of revascularization based on theresult of the comparison.

According to some embodiments of the invention, further includingassessment of a current ischemic condition based on the result of thecomparison.

According to an aspect of some embodiments of the present inventionthere is provided apparatus for analyzing a high frequency (HF)electrogram signal including an electrode for use inside a living body,a signal pickup configured to pick up an electrogram signal including ahigh frequency (HF) component, a measurement unit for measuring a highfrequency (HF) component from the electrogram signal during a specificsegment of a cardiac cycle, and an analyzer for analyzing the HFcomponent of the electrogram signal, wherein the analyzer is configuredto compare at least one time-varying parameter of the HF electrogramsignal measured at a first location within a subject's body and at leastone time-varying parameter of the HF electrogram signal measured at asecond location within a subject's body, and to produce a result of thecomparison.

According to some embodiments of the invention, further including asetting for determining whether stent therapy is needed based on theresult of the comparison.

According to some embodiments of the invention, further including asetting for post-revascularization assessment of revascularization basedon the result of the comparison.

According to some embodiments of the invention, further including asetting for assessment of a current ischemic condition based on theresult of the comparison.

According to an aspect of some embodiments of the present inventionthere is provided a method for analyzing a high frequency (HF)electrogram signal including (a) providing at least one electrogramsignal between a first electrode at a first location within a subject'sbody and a second electrode at a second location within a subject'sbody, the first location and the second location being adjacent to aheart, opening at least a 90 degree angle relative to a direction towarda center of mass of the heart, (b) measuring the electrogram signal at ahigh frequency generating a HF electrogram signal, (c) having a computermeasure at least one time-varying parameter of the HF electrogramsignal, (d) having a computer detect a change in the time-varyingparameter in comparison to a baseline value of the time-varyingparameter, and (e) having the computer generate an alert based, at leastin part, on the detection.

Unless otherwise defined, all technical and/or scientific terms usedherein have the same meaning as commonly understood by one of ordinaryskill in the art to which the invention pertains. Although methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of embodiments of the invention, exemplarymethods and/or materials are described below. In case of conflict, thepatent specification, including definitions, will control. In addition,the materials, methods, and examples are illustrative only and are notintended to be necessarily limiting.

Implementation of the method and/or system of embodiments of theinvention can involve performing or completing selected tasks manually,automatically, or a combination thereof. Moreover, according to actualinstrumentation and equipment of embodiments of the method and/or systemof the invention, several selected tasks could be implemented byhardware, by software or by firmware or by a combination thereof usingan operating system.

For example, hardware for performing selected tasks according toembodiments of the invention could be implemented as a chip or acircuit. As software, selected tasks according to embodiments of theinvention could be implemented as a plurality of software instructionsbeing executed by a computer using any suitable operating system. In anexemplary embodiment of the invention, one or more tasks according toexemplary embodiments of method and/or system as described herein areperformed by a data processor, such as a computing platform forexecuting a plurality of instructions. Optionally, the data processorincludes a volatile memory for storing instructions and/or data and/or anon-volatile storage, for example, a magnetic hard-disk and/or removablemedia, for storing instructions and/or data. Optionally, a networkconnection is provided as well. A display and/or a user input devicesuch as a keyboard or mouse are optionally provided as well.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWING(S)

Some embodiments of the invention are herein described, by way ofexample only, with reference to the accompanying drawings. With specificreference now to the drawings in detail, it is stressed that theparticulars shown are by way of example and for purposes of illustrativediscussion of embodiments of the invention. In this regard, thedescription taken with the drawings makes apparent to those skilled inthe art how embodiments of the invention may be practiced.

In the drawings:

FIG. 1A is a simplified illustration of a prior art apparatus fordetecting myocardial ischemia using analysis of high frequencycomponents of an electrocardiogram;

FIG. 1B is a simplified illustration of typical prior art locations forattaching pickup electrodes, including electrodes for picking up highfrequency components of an electrocardiogram;

FIG. 2A is a simplified illustration of apparatus for analyzing anelectrogram according to an example embodiment of the invention;

FIG. 2B is a simplified illustration of some non-limiting examplepotential differences measured by the example embodiment of FIG. 2A;

FIG. 2C is a simplified illustration of apparatus for analyzing anelectrogram and some non-limiting example potential differences,according to an example embodiment of the invention;

FIG. 2D is a simplified illustration of apparatus for analyzing anelectrogram according to an example embodiment of the invention;

FIG. 2E is a simplified illustration of apparatus for analyzing anelectrogram according to an example embodiment of the invention;

FIG. 2F is a simplified illustration of apparatus for detectingmyocardial ischemia using analysis of high frequency components of anelectrogram according to an example embodiment of the invention;

FIG. 2G is a simplified illustration of apparatus for detectingmyocardial ischemia using analysis of high frequency components of anelectrogram according to an example embodiment of the invention;

FIGS. 2H and 2I are graphs showing good correlation and bad correlationof HF signals according to an example embodiment of the invention;

FIG. 2J depicts graphs of HF signals of 16 different QRS complexesaccording to an example embodiment of the invention;

FIG. 2K depicts a graph of alignment of an unfiltered electrogram signalto a template according to an example embodiment of the invention;

FIG. 2L is a graph depicting an HF portion of an inherent electrogramsignal and an actual HF signal, according to an example embodiment ofthe invention;

FIG. 3 is a simplified prior art illustration of effects of breathing onelectrocardiogram signals;

FIG. 4A is a simplified illustration of electrodes for picking up anelectrogram within a blood vessel according to an example embodiment ofthe invention;

FIG. 4B is a simplified illustration of electrodes for picking up anelectrogram within a blood vessel according to an example embodiment ofthe invention;

FIG. 5 is a flow chart of a method for analyzing a high frequency (HF)electrogram signal according to an example embodiment of the invention;

FIG. 6 is a flow chart of a method for analyzing a high frequency (HF)electrogram signal according to an example embodiment of the invention;

FIG. 7A is a flow chart of a method for analyzing a high frequency (HF)electrogram signal according to an example embodiment of the invention;and

FIG. 7B is a flow chart of a method for analyzing a high frequency (HF)electrogram signal according to an example embodiment of the invention.

DESCRIPTION OF SPECIFIC EMBODIMENTS OF THE INVENTION

The present invention, in some embodiments thereof, relates to anapparatus and method for detecting myocardial ischemia using analysis ofhigh frequency components of an electrocardiogram and/or of a cardiacelectrogram, and, more particularly, but not exclusively, to animplantable such apparatus and method.

A broad aspect of some embodiments of the invention relates to measuringa HF (high frequency) electrogram from inside the body, for example,using electrodes which are also used for IPGs (implantable pulsegenerators), for example, for a pacemaker, a cardiac resynchronizationtherapy (CRT) and/or a defibrillator or cardioverter, or otherimplantable devices with signal sensing capabilities likeneurostimulators or implantable electrogram recorders.

An aspect of some embodiments of the invention relates using asignificant amount of collected data to reduce noise and/or increasesensitivity of HF electrogram measurements. In typical, out of body HFelectrocardiogram measurements, the signal is often noisy and it isdifficult to measure long periods while the heart is stressed (e.g., ina stress test). In an exemplary embodiment of the invention, use is madeof an implantable measurement device to provide a high qualityintracardiac electrogram signal, providing a significant amount of data,potentially over a period of hours, days, weeks, months, even years. Thesignal is collected on a routine basis and HF electrogram values aremeasured for recording of long term values that sometimes serve as abaseline for clinical diagnosis and long term status of the subject andshort term values that provide an indication on a current transientstatus. In an exemplary embodiment of the invention, the data is used toprovide a reliable baseline. Optionally or alternatively, the data isused to provide a baseline for multiple categories, for example,different baselines for different values of physiologically relatedand/or measured parameters (e.g., one or more of movement, bloodpressure, time of day, ischemia, eating, sleeping), ECG morphologies,breathing cycle portions and/or types, pacing activity and/orparameters, heart rate. Optionally or alternatively, the data is used toanalyze simultaneously two or more HF electrogram parameters, such asamplitude and morphology, potentially providing a more robust analysisof the subject's condition.

In some embodiments, a result of the analysis of the electrogram signalis optionally stored. In some embodiments, the analysis and/or thestoring include compression of the result of the analysis.

An aspect of some embodiments of the invention relates to changingbehavior of an IPG based on results of the analysis. In someembodiments, the IPG changes pulse generation timing based on theresults of the analysis. In some embodiments, a CRT changes output basedon the results of the analysis.

An aspect of some embodiments of the invention relates to synchronizingthe acquisition and/or analysis of HF electrogram signals to a breathingparameter. In an exemplary embodiment of the invention, it is noted thatthe breathing cycle has an effect on the autonomous nervous system andon various actions and reactions of the heart. In an exemplaryembodiment of the invention, measurement comprises binning measurementsaccording to a breath cycle.

An aspect of some embodiments of the invention relates to synchronizingdata acquisition and/or analysis activities to particular parts of thecardiac cycle and/or local electrical activity. Optionally, anacquisition window is defined, for example, based on an estimated timewhen a signal of interest is expected (e.g., based on a pacing signal oran analysis of a previous signal) and/or based on a trigger signal(e.g., a local sensing of electrical activity at the measurementlocation or remote therefrom). In an exemplary embodiment of theinvention, only data acquired in the window is analyzed and/or acquiredat high frequency.

In some embodiments, the acquisition window is optionally opened basedon an estimated time following reception of a pacing signal.

In some embodiments, the acquisition window is optionally opened basedon detecting a specific point in a low-frequency electrogram signal,such as, by way of a non-limiting example, a beginning of a QRS complex,or a P segment, or a Q segment, or a R segment, or a S segment, or a Tsegment.

In some embodiments, the acquisition window is optionally opened basedon a signal indicating a specific physiological condition, such as aspecific portion of a breathing cycle, as described in more detail belowwith reference to FIG. 3.

In some embodiments, the acquisition window is closed based on detectinga specific point in a low-frequency electrogram signal, such as, by wayof a non-limiting example, an end of a QRS complex, or a P segment, or aQ segment, or a R segment, or a S segment, or a T segment.

In an exemplary embodiment of the invention, the measured HF electrogramsignal is not of an entire QRS complex, rather the measurement reflectsa segment of the QRS complex. In some cases this segment relates to thelocation of the implantable electrode location.

In an exemplary embodiment of the invention, the portion of the cardiaccycle which is acquired and/or analyzed is less than 50%, 30%, 20%, 10%,5% or intermediate percentages of the time.

In an exemplary embodiment of the invention, selective data acquisitionis applied in conjunction with such synchronizing, for example,acquiring and/or analyzing HF electrogram signals only if both timingand one or more other criteria are met. For example, acquisition maydepend on both breathing cycle and time in cardiac cycle. For example,acquisition may be performed during similar physiological conditionssuch as similar pulse rate, during a subject's sleep, etc. by way of anon-limiting example, sleeping is optionally detected by measuring heartrate and/or heart rate variability.

An aspect of some embodiments of the invention relates to measuringlocal HF electrogram signals, for example, between two electrodes thatare at or near the heart, rather than between an electrode in the heartand an electrode far from the heart. In an exemplary embodiment of theinvention, this allows an HF electrogram signal to be mostly of a smallpart of the heart (e.g., less than 50%, 40%, 30%, 20%, 10% orintermediate percentages of a muscle mass volume thereof). In anexemplary embodiment of the invention, the measurement is using bipolarelectrodes (or other multiple electrodes on a same lead) which measureHF electrogram contributions from nearby tissue, for example, to withina distance of less than 5 cm, 3 cm, 2 cm, 1 cm or intermediatedistances. Optionally or alternatively, the measurement is usingseparate electrodes, for example, one atrial electrode and oneventricular electrode, and the measured tissue lies between the pair ofelectrodes. In some embodiments more than two electrodes are used. Insome embodiments two or more electrodes are used and their signalsoptionally combined, optionally averaging the signals provided by both.

In some embodiments, the HF electrogram is optionally picked up and/ormeasured and/or analyzed excluding times when a pacing signal isprovided by a pacing unit.

In an exemplary embodiment of the invention, at least one electrode isplaced so that a significant part of the heart can be assessed, forexample, at least 30%, 50%, 60% or intermediate parts of the heart.Optionally, such measurement is between an intra-cardiac electrode or anelectrode adjacent the heart and the can of an IPG or a remote electrodeor an electrode at another side of the heart. It is noted that measuringa signal between electrodes placed at different locations potentiallyenables measuring the difference in tissue between a source of anelectric signal (natural or artificial pacing) and the electrodelocation.

An aspect of some embodiments of the invention relates to identifyinglocal ischemia by comparing a first measurement and a second measurementwhich are separated in time and/or space. In some embodiments, a valueof a function of several measurements which are separated in time and/orspace may be computed in order to compare values of the function and/orto derive a clinical indicator.

By way of a non-limiting example, calculating a base line value at aspecific time when it is clear that a patient is not showing sign ofischemia. Such measurement and/or calculation may optionally be doneduring a physician check up, and/or during a specific time of the day,and/or during low heartrate (HR) value, for example a lowest HR valueevery day, and/or during sleep, optionally during a deep sleep stage. Insome embodiments a baseline is optionally measured during a period witha highest HR variability during a day. In some embodiments the baselinevalue is optionally compared to a measured value at a different time. Insome embodiments the different time is optionally a selected timing suchas a time with a specific heartrate, and/or during exercise activity,and/or during REM sleep, and/or during a time with minimal heart ratevariability during the day

In an exemplary embodiment of the invention, the criticality of astenosis or other vascular flow abnormality is determined by measuringHF electrogram components upstream and downstream (or within) theabnormality. It is expected that significant (e.g., should be treated)abnormalities will show a significant difference in ischemia between theupstream and downstream locations. A non-limiting example difference mayoptionally be a change in HF RMS values greater than 2%, 5%, 10% or 20%,30%, 40% or 50%.

In another example, ischemia levels at difference localities aremeasured using pairs of electrodes as described above. Optionally, thiscomparison is used to assess progress of treatment and/or disease and/orto determine changes in ischemia in different parts of the heart as afunction of condition (e.g., physiological state, stress, sleep).

In an exemplary embodiment of the invention, the comparison is overtime, by comparing the degree of ischemia under different conditions.

In an exemplary embodiment of the invention, electrode placement isselected to ensure the ability to measure desired localities and/orcompare such localities.

An aspect of some embodiments of the invention relates to electrogramsignals gathered from implanted electrodes being stronger thanelectrocardiogram signals gathered from electrodes attached to asubject's skin.

In some embodiments, the implanted electrodes are optionally connected,directly or wirelessly, to an analyzer external to a subject's body. Insome embodiments, the implanted electrodes are optionally connected toan analyzer also implanted in the subject's body. In some embodiments,at least one electrode, or at least a reference potential, is measuredat the implanted analyzer body, also termed a can.

In some embodiments, the implanted electrodes are optionally connectedto an IPG, optionally a pacemaker with processing capabilities, and theanalyzer is included in the IPG can. In some embodiments the analyzerincludes adding components to a pacemaker, in some embodiments theanalyzer includes software which runs on a pacemaker processor.

In some embodiments, the same electrodes used for measuring theelectrogram or for providing a pacing signal by the pacemaker, CRT, ICDor any other implantable device are optionally used to pick up theelectrogram.

In some embodiments, the electrogram signal is not picked up while apacing signal is provided by the pacemaker. Since the pacing signal isshort, typically on the order of one millisecond, once per heartbeat,the same electrodes used for pacing can optionally be used to pick upthe electrogram during the rest of the time.

In some embodiments, the electrogram signal is not picked up for 5, 10,15, 20, 25, 30 or even 50 milliseconds following a pacing signal by thepacemaker. In some embodiments, a QRS complex signal triggered by pacingis not picked up. In some embodiment, the smart pacemaker provides asignal to an electrogram pickup unit, and the electrogram pickup unit isthus notified when a QRS complex signal is triggered by pacing.

Modern pacemakers do not provide pacing signals all the time, onlyresponsive to a subject's heart rate and/or heart condition. In suchpacemakers the same electrodes used for pacing are optionally used topick up the electrogram, since the electrodes are not being used toprovide pacing signals during most of the time.

An aspect of some embodiments of the invention relates to the strongerelectrogram signals being synergistically conducive to analyzing highfrequency (HF) electrocardiogram signals, which are weak when gatheredfrom electrodes attached to a subject's skin. Potentially, various knowntechniques such as described in the references listed in the Backgroundsection, are able to be carried out with less interfering noise,potentially at higher quality, potentially at higher signal to noiseratio (SNR), potentially over shorter measurement durations.

An aspect of some embodiments of the invention relates to alignment ofthe electrogram signals.

In some embodiments alignment of electrogram signals from differentheart beats is optionally performed by correlation of low frequencycomponents of the electrogram signals, and/or by correlation of highfrequency components of the electrogram signals, and/or by synchronizingrelative to a pacemaker pulse, and/or by synchronizing relative todetected atrial depolarization by using an atrial electrode. In someembodiments the alignment is of an electrogram signal to an inherentelectrogram signal, as will be described further below.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering electrogram signals only during aspecific fraction of time, potentially lengthening duration of operationbetween possible battery charging and/or battery replacing.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering electrogram signals only during aspecific fraction of the cardiac cycle.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering electrogram signals only during aspecific fraction of the QRS complex segment of the cardiac cycle.

An aspect of some embodiments of the invention relates to saving powerin an implanted device by gathering electrogram signals only during aspecific fraction of a breathing cycle, potentially comparing likesignals to like signals, since some features of an electrogram signaltypically correlate to the breathing cycle, and potentially lengtheningduration of operation between possible battery charging.

An aspect of some embodiments of the invention relates to measuring theHF electrogram when the heart rate is within a specific range of heartrates.

An aspect of some embodiments of the invention relates to electrogramsignals gathered from implanted electrodes enabling placing theelectrodes at locations physiologically different than only electrodesattached to a subject's skin.

An aspect of some embodiments of the invention relates to analyzing highfrequency (HF) electrogram signals which are picked up proximally anddistally to an occlusion in a blood vessel. Comparing theabove-mentioned signals potentially indicates a change in tissue beforeand after the occlusion, and/or a degree of the occlusion. In someembodiments, the comparison of the HF electrogram signals may optionallybe performed in a same procedure as performing a fractional flow reserve(FFR) measurement, and results of both measurements may be combined toindicate degree of the occlusion and/or suggest a method of treatment ofthe occlusion.

For purposes of better understanding some embodiments of the presentinvention, reference is first made to FIG. 1A, which is a simplifiedillustration of a prior art apparatus for detecting myocardial ischemiausing analysis of high frequency components of an electrocardiogram.

FIG. 1A depicts a thorax 105, with electrodes 107 attached to the thorax105 and to a device 109 for analysis of high frequency components of anelectrocardiogram.

Reference is also made to FIG. 1B, which is a simplified illustration oftypical prior art locations for attaching pickup electrodes, includingelectrodes for picking up high frequency components of anelectrocardiogram.

FIG. 1B depicts three line FIGS. 151 152 153 of human subjects, andthree sets of locations 155 156 157 for placing electrodes for pickingup high frequency components of an electrocardiogram.

Before explaining at least one embodiment of the invention in detail, itis to be understood that the invention is not necessarily limited in itsapplication to the details of construction and the arrangement of thecomponents and/or methods set forth in the following description and/orillustrated in the drawings and/or the Examples. The invention iscapable of other embodiments or of being practiced or carried out invarious ways.

Reference is now made to FIG. 2A, which is a simplified illustration ofapparatus for analyzing an electrogram according to an exampleembodiment of the invention.

FIG. 2A shows a schematic depiction of a chest 202, with an implantedelectronics box, also termed an implantable device 204 also termed acan, and with one or more electrodes electrically connecting the device204 with one or more electrogram signal pickup locations. Example pickuplocations depicted in FIG. 2A include the right atrium 222, the rightventricle 224, the left atrium 230, and the left ventricle 226. Theelectrogram signal pickup locations may optionally be located on asurface of the heart at epicardial locations. The electrogram signalpickup locations may optionally also be located in coronary veins andarteries such as the coronary sinus. The electrogram signal pickuplocations may also be at some other place in a subject's thorax 228.FIG. 2A also depicts a schematic drawing of a heart 220.

The example embodiment of FIG. 2A depicts a first electrode locationoptionally located at the right atrium 222; a second electrode locationoptionally located at the right ventricle 224; a third electrodelocation optionally located at the left ventricle 226; and a fourthelectrode location optionally located elsewhere in the thorax 228. Theleft atrium 230 of the heart is shown without an electrode in thepresent example embodiment.

It is noted that the device 204 is depicted as a schematic block, notnecessarily depicted at the best location for the implantation.

In some embodiments the device 204 can is at least partially conductiveand may optionally serve as an additional electrogram signal pickuplocation.

It is noted that some embodiments may optionally include an electrodelocated at the left atrium 230. In some embodiments there may optionallybe an electrode located at the left atrium 230 for use in pacing,optionally without using the electrode for electrogram pickup.

Example Electrode Locations

In some example embodiments the electrogram signal is measured betweentwo electrodes which are placed both in the same heart chamber.

In some example embodiments the electrogram signal is measured betweenan electrode which is placed in a heart chamber and an electrode whichis placed outside the heart chamber.

In some example embodiments the electrogram signal is measured betweenan electrode which is placed in a first heart chamber and an electrodewhich is placed in a second heart chamber.

In some example embodiments the electrogram signal is measured betweenan electrode which is placed touching a heart an electrode which iselectrically coupled to a device can.

In some example embodiments the electrogram signal is optionallymeasured between two locations adjacent to a heart, the two locationshaving at least 50% of the mass of the heart between them.

In some example embodiments the electrogram signal is measured betweenan intracardiac electrode and an epicardiac electrode.

Reference is now additionally made to FIG. 2B, which is a simplifiedillustration of some non-limiting example potential differences measuredby the example embodiment of FIG. 2A.

FIG. 2B depicts the schematic depiction of the chest 202, the device204, the electrogram signal pickup locations 222 224 226 228 230, andthe schematic depiction of the heart 220, as also shown in FIG. 2A.

FIG. 2B demonstrates some non-limiting examples of potential differences251-257 measured between the electrogram signal pickup locations 204 222224 226 228. The examples of potential differences 251-257 are a partialexample of pairing of the locations 204 222 224 226 228 230.

In some examples, where bipolar electrodes are used, an electrogramsignal may also optionally be measured between two poles on the samegeneral location 204 222 224 226 228 230.

In some embodiments the system optionally performs simultaneousmeasurement of several electrogram signals from several pairs ofelectrodes, providing measurement of several electrogram vectors and/orindexes.

Reference is now additionally made to FIG. 2C, which is a simplifiedillustration of apparatus for analyzing an electrogram and somenon-limiting example potential differences, according to an exampleembodiment of the invention.

FIG. 2C demonstrates use of subcutaneous thoracic and/or abdominalelectrodes and optionally use of a device “can”, as an electrode.

FIG. 2C depicts the schematic depiction of the chest 202, the device204, the electrogram signal pickup locations 204 222 224 226 230 281282, and the schematic depiction of the heart 220.

FIG. 2C demonstrates some non-limiting examples of potential differences291-296 and 255-257 measured between electrogram signal pickup locations204 222 224 226 230 281 282. The examples of potential differences291-296 and 255-257 are a partial example of pairing of the locations204 222 224 226 230 281 282.

FIG. 2C specifically demonstrates locations 281 and 282 which areexamples of subcutaneous thoracic and/or abdominal electrodes. In someembodiments the system may include 1, 2 or more thoracic and/orabdominal electrodes. In some embodiments, the device “can”, depicted byreference number 204, is optionally also placed subcutaneously andoptionally serves as an electrode.

It is noted that electrical potential differences are optionallymeasured between a pair of thoracic and/or abdominal electrodes, such asthe potential difference 291, and/or between a thoracic and/or abdominalelectrode and the device “can”, such as the potential differences 292293, and/or between a subcutaneous “can” and an intra-cardiac electrode,such as the potential difference 294, and/or between a thoracic and/orabdominal electrode and an intra-cardiac electrode, such as thepotential differences 295 296.

In some examples, where bipolar electrodes are used, an electrogramsignal may also optionally be measured between two poles on the samegeneral location 204 222 224 226 230 281 282.

In some embodiments the system optionally performs simultaneousmeasurement of several electrogram signals from several pairs ofelectrodes, providing measurement of several electrogram vectors and/orindexes.

Reference is now additionally made to FIG. 2D, which is a simplifiedillustration of apparatus for analyzing an electrogram according to anexample embodiment of the invention.

FIG. 2D shows a schematic depiction of a chest 202, with an implantabledevice 235, also termed a can, and with one monopole electrodeelectrically connecting the device 235 with an electrogram signal pickuplocation 226, optionally in the coronary sinus at a location inproximity to the left ventricle. FIG. 2D also depicts a schematicdepiction of the heart 220. The electrode location may optionally be ona surface of the heart 220, optionally using an epicardial electrode,optionally attached and/or sutured to the surface of the heart 220.

It is noted that there are optionally many alternative configurations ofmeasuring potential differences for producing an electrogram. Theconfigurations include, by way of some non-limiting examples:

a monopole electrode and the can; a bipolar electrode at each one ofseveral heart locations (for example as shown in FIGS. 2A-2C);

between any 2 electrode positions in the heart, e.g. intracardiac,epicardiac (on the heart), in coronary blood vessels. By way of anon-limiting example—between the right atrium and the left ventricle;

between an electrode in the heart and an electrode in the thorax (forexample as shown in FIGS. 2A-2C);

between two locations in the thorax (not shown); and

between locations some of which are positioned at a cardiac bloodvessel.

In some embodiments a bipolar electrode may optionally serve to measurea potential difference between two poles of the bipolar electrode.

In some embodiments a monopolar electrode may optionally serve tomeasure a potential difference between the monopolar electrode and thedevice can, and/or relative to a different electrode, whether thedifferent electrode is another monopolar electrode or a bipolarelectrode.

In various embodiments electrogram vectors are optionally produced fromthe potential differences measured. In various embodiments HF indexes,for example such as described in U.S. Pat. No. 8,626,275, are optionallycalculated for some or all of the electrogram vectors.

In some embodiments at least the following HF indexes are optionallyused: an RMS of the HF electrogram; an amplitude of the HF electrogram;and a morphology of the HF electrogram.

Reference is now made to FIG. 2E, which is a simplified illustration ofapparatus for analyzing an electrogram according to an exampleembodiment of the invention.

FIG. 2E shows a schematic depiction of a chest 240, with a device 242,also termed a can, external to the chest 240, and with one or moreelectrodes 244 electrically connecting the device 242 with one or moreelectrogram signal pickup locations located within the subject's body(not shown).

FIG. 2E depicts an example embodiment in which the device 242 isexternal to the subject's body, while the electrodes 244 extend to oneor more electrogram signal pickup locations located within the subject'sbody (not shown).

In some embodiments the device 242 is not necessarily attached to thesubject's body.

In some embodiments electrodes (not shown) are entirely implanted withthe subject's body, and a device (not shown) inside the subject's bodysends wireless signals to a receiver (not shown) outside the subject'sbody.

Reference is now made to FIG. 2F, which is a simplified illustration ofapparatus for detecting myocardial ischemia using analysis of highfrequency components of an electrogram according to an exampleembodiment of the invention.

FIG. 2F shows a schematic depiction of an implantable device 260, whichincludes an HF electrogram analyzer 262 and a pacemaker 264. In FIG. 2Fthe HF electrogram analyzer 262 optionally shares one or more electrodes266 with the pacemaker 264. The analyzer 262 is optionally connected 263to the same electrodes 266 to which the pacemaker 264 is also connected265.

FIG. 2F depicts an example embodiment in which the analyzer 262 sharesthe can 260 with a pacemaker 264, and also shares the electrodes 266.

In some embodiments, the analyzer 262 is optionally connected 268 to abody of the can 260.

In some embodiments, the analyzer 262 optionally communicates with thepacemaker 264, for example in order to receive a signal when thepacemaker 264 sends a pacing signal.

Reference is now made to FIG. 2G, which is a simplified illustration ofapparatus for detecting myocardial ischemia using analysis of highfrequency components of an electrogram according to an exampleembodiment of the invention.

FIG. 2G shows a schematic depiction of an implantable device 270, whichan HF electrogram analyzer 272 shares with a pacemaker 274. In FIG. 2Gthe HF electrogram analyzer 272 is connected 273 one or more electrodes279 not shared with the pacemaker 274, and the pacemaker is connected275 to one or more electrodes 276 not shared with the analyzer 272.

FIG. 2G depicts an example embodiment in which the analyzer 272 sharesthe implantable device 270 with the pacemaker 274, and does not alsoshare the electrodes.

In some embodiments, the analyzer 272 is optionally connected 278 to abody of the can 270.

In some embodiments, the analyzer 272 optionally communicates with thepacemaker 274, for example in order to receive a signal when thepacemaker 274 sends a pacing signal.

The present invention, in some embodiments thereof, relates toquantification of high frequency signals of the electrogram within asetting of an implantable device, and/or intracardiac electrodes and/orintracoronary electrodes.

The term endocardiac electrode refers to electrodes which are placed inthe heart and typically used for mapping, and the term intracardiacelectrodes refers more to single lead electrodes for pacing and/orsensing.

The term epicardial electrode refers to electrodes which are placed on aheart, beneath the pericardium.

In various embodiments, endocardiac electrode(s), and/or intracardiacelectrode(s) and/or epicardial electrode(s) are used.

In various embodiments, monopolar electrodes and/or bipolar electrodesand/or multipolar electrodes or a mix thereof are used.

In some embodiments the implantable device has an independent sensingand analysis device, even if contained within a can of a pacemaker.

In some embodiments the implantable device transmits signals by wirelesstransmission to a receiver located outside a body of a subject in whichthe device is implanted. In some embodiments the transmitted signalincludes raw data. In some embodiments the transmitted signal includesresults of an analysis and/or an alert signal. In some embodiments theimplantable device transmits signals by a wired connection to a receiverlocated outside a body of a subject in which the device is implanted.

In some embodiments the alert is an alert sent to a human and/or to acomputer circuit and/or program and/or receiver.

In some embodiments the implantable device is used in conjunction withother implantable devices such as a pacemaker, an implantablecardioverter defibrillator (ICD), a neural stimulator, an implantablepump, a stent, artificial valves, or a cardiac resynchronization therapy(CRT) device.

In some embodiments the implantable device shares a can and/orelectrodes with the above-mentioned implantable devices.

In some embodiments the implanted device optionally uses implantableelectrodes for sensing an electrogram. Such electrodes are optionallyplaced on a surface of the device (which is implanted inside thesubject's body, optionally close to the heart), and/or removablyattached to the device and placed in proximity of a heart inintracardiac or/and endocardial and/or intracoronary positions.

In some embodiments the device optionally measures an electrogram signalbetween 2 electrodes and/or between several pairings of electrodes. Insome embodiments the device optionally measures an electrogram signalbetween an electrode and a location on a can of the implantabledevice—optionally on a surface of the implantable device.

In some embodiments, high frequency analysis of the QRS complex segmentof the electrogram is optionally used for detecting myocardial ischemia.The high frequency analysis optionally calculates one or more parametersbased on the high frequency electrogram signal.

In some embodiments, detecting ischemia, or calculating a parameterbased on the high frequency electrogram signal which can potentiallyindicate ischemia, optionally causes sending an alert to a pacemaker.

In some embodiments, detecting ischemia, or calculating a parameterbased on the high frequency electrogram signal which can potentiallyindicate ischemia, occurs inside an implantable device such as apacemaker or other implantable device.

In some embodiments, a P-wave interval is evaluated for detection ofatrial fibrillation onset and/or for indication of potential futureonset of atrial fibrillation, and/or an irregular propagation of anaction potential in a cardiac atria, and/or atrial tachycardia, and/oratrial bradycardia, and/or atrial arrhythmia.

In some embodiments, upon detection of onset of atrial arrhythmia, orindication of potential future onset of atrial arrhythmia, a signal isproduced to initiate anti- arrhythmia pacing.

In some embodiments, upon detection of onset of atrial fibrillation, orindication of potential future onset of atrial fibrillation, adefibrillator is optionally instructed to charge.

In some embodiments, upon detection a condition such as onset of atrialfibrillation, and/or indication of potential future onset of atrialfibrillation, and/or an irregular propagation of an action potential ina cardiac atria, and/or atrial tachycardia, and/or atrial bradycardia,and/or atrial arrhythmia, a signal is produced to stop a pacemaker fromproducing signals which induces the above condition(s).

In some embodiments the apparatus is optionally tuned so as to reduceand/or stop a detected condition.

In some embodiments, ischemia is detected by detecting a reduction in HFECG intensity, and/or a change in amplitude of an ST segment of the HFECG signal. Following detection of ischemia, for example, thereducing/stopping optionally includes reducing a pacing rate by a presetnumber of beats-per-minute or by a preset percentage of the heart rate.In some embodiments the reduction is optionally adjusted by measuring anindication of the ischemia level, and optionally reducing the pacingrate in a closed-loop feedback manner which monitors the indication ofthe level of ischemia and sets the pacing rate accordingly.

In some embodiments, atrial arrhythmia is detected by a significantchange in the P wave HF ECG morphology. Optionally, upon detecting onsetof atrial arrhythmia, the pacing rate is manipulated to overcome theatrial arrhythmia. By way of a non-limiting example, such a manipulationincludes increasing the pacing rate to control the rate and thengradually decrease the rate back to normal values.

For atrial fibrillation, for example, the reducing/stopping optionallyincludes modulation of a pacing signal so as to overcome the atrialfibrillation, for example by increasing the heart rate to gain controlover the heart-rate, optionally followed by reducing the heart-rate toreach lower values. In some embodiments the reducing/stopping isoptionally done by a high atrial pacing, which optionally takes over anatural fibrillation rate, optionally followed by decreasing the atrialpacing rate.

In some embodiments an electrogram signal which is detected to have ahigh HF content and/or a fluctuation in HF content of the P waveoptionally causes a determination of a potential for developingarrhythmia. The determination may optionally cause producing a warning.

In some embodiments the following parameters are calculated based on thehigh frequency electrogram signal and high frequency ECG analysis:

-   -   an RMS of the high frequency signal of the QRS complex, which        typically decreases during ischemia;    -   detection and quantification of a reduced amplitude zone (RAZ)        in the high frequency signal of the QRS complex.

The high frequency electrogram is optionally measured in variousconfigurations allowing for the analysis of electrical activity inmultiple vectors according to the location of the electrodes relative tothe device's can and/or between pairs of electrodes and/or combinationsof electrodes.

Locations for the Implantable Device

The implantable device for the electronics for performing at least thepickup of the HF signals, as well as optionally the pickup ofregular-frequency ECG signals, in different embodiments, may be foundas:

an implanted device, by way of a non-limiting example such as depictedin FIGS. 2A, 2B and 2D;

an external device, by way of a non-limiting example such as depicted inFIG. 2E.

In some embodiments an implanted device is optionally included in apacemaker can, optionally a smart pacemaker.

In some embodiments an implanted can is optionally a can implantedseparately from an existing pacemaker, if any.

In some embodiments the can optionally serves for HF electrogram signalpickup, and transfers the signals to an external analysis unit. In someembodiments the transfer of the signals is optionally performedwirelessly. In some embodiments the transfer of the signals isoptionally performed by wire.

Internal/External Electrodes

In some embodiments the pickup electrodes are implanted electrodescommon with pacemaker electrodes.

In some embodiments the pickup electrodes are implanted electrodesseparate from pacemaker electrodes.

In some embodiments the pickup electrodes are inserted into a subject'sbody via a catheter, and optionally used while the catheter is insidethe subject's body, without being implanted.

Electrode Locations

In various embodiments the pickups are located in various locations,such as, by way of some non-limiting examples:

a right atrium (RA);

a right ventricle (RV);

a left ventricle (LV);

a coronary sinus (CS);

an epicardial location; and

an electrode located in the chest.

Internal/External Analysis

In some embodiments analysis of the HF electrogram signals is performedwithin an implanted can.

In some embodiments analysis of the HF electrogram signals is performedexternally of a subject's body.

During Angiogram/Angio-Stent

In some embodiments monitoring and/or analysis of the HF electrogramsignals is performed during a procedure in which electrodes are insertedinto a subject's body, such as, by way of a non-limiting example, duringan angiogram, with electrodes inserted via catheter.

Detecting the QRS Complex

In some embodiments, a temporal location of the QRS complex isoptionally detected by analyzing a signal from an electrode in the rightatrium.

A natural heart pacing starts at the right atrium.

In some embodiments detecting onset of a pulse optionally provides anindication when to start recording at a HF sampling rate.

In some embodiments HF sampling is optionally synchronized with apacemaker pacing pulse.

In some embodiments an estimation is made as to when a next QRS complexsignal is expected based on timing and rate of previous heart beats.

HF Sampling in a Sub-Portion of the Cardiac Cycle

The terms cardiac cycle portion, cardiac cycle sub-portion and cardiaccycle segment are used interchangeably in the specification and claims.

In some embodiments, especially implantable embodiments, power andcurrent consumption may impose constraints on the device and/or methodof detection and monitoring of myocardial ischemia. In such embodimentsit is preferable to save in power consumption of the device.

In some embodiments, to facilitate the saving, a specific mode of thedevice is optionally configured to sample the electrogram at a highsampling rate., e.g. 1000 samples per second, only during specificportions of the signal or of the cardiac cycle, e.g. during and aroundthe QRS complex. At other times, which typically constitute more than50% and up to 90% of the cardiac cycle, the signal may be sampled at alower frequency, for example, fewer than 150 samples per second. In someembodiments, the sampling rate is lowered even further, and/or suspendedaltogether.

In some embodiments the device is optionally configured to perform HFsampling only during, by way of some non-limiting example:

the QRS complex interval;

the P wave interval;

the T wave interval;

the Q wave interval:

the R wave interval; and

the S wave interval.

In some embodiments, a beginning and/or and end of the segment of thecardiac cycle is defined to start and/or end based, by way of somenon-limiting examples, on one or more of:

detection of a specific point in a cardiac cycle, optionally usinganalysis of the HF electrogram and/or a low frequency ECG;

a timing offset from a trigger such as the above specific point, forexample a P wave maximum plus 10 milliseconds; and

a timing offset from a trigger such as a pacing signal, for example a Pwave maximum plus 10 milliseconds.

Generally, high frequency signals are analyzed in a range of frequenciesbetween 100 and 1000 Hz, and low frequency ECG signals are analyzed in arange of frequencies between 0.05 and 100 Hz. In some embodimentsanalysis of the high frequency signal samples is optionally performedfor a frequency between 100 and 300 Hz, optionally with signals sampledat a rate of 1000 Hz or more. In some embodiments analysis of the highfrequency signal samples is optionally performed for a frequency above500 Hz.

In some embodiments an intracardiac electrogram is measured during a QRScomplex with a high sampling rate, and during a rest of the cardiaccycle using low sampling rate. Some non-limiting example include a highsampling rate greater than 500 samples per second, and even greater than1,000 samples per second. Some non-limiting example include a lowsampling rate greater than 150 samples per second, lower than 100samples per second, and even lower than 60 samples per second.

In some embodiments detecting the QRS complex is performed by detectingthe QRS complex in a low frequency electrogram, that is, detecting theQRS complex in a regular ECG.

In some embodiments detecting the QRS complex is performed by detectingthe QRS complex by analyzing a high frequency electrogram.

Cleaning up the HF Signal

The high frequency signal used for detecting myocardial ischemia may berelatively low in amplitude, even for intracardiac signals. In someembodiments the HF signal is optionally aligned and averaged overseveral QRS complexes which are close in time. Such an averagingprocedure potentially increase the SNR (Signal to Noise Ratio),potentially enabling a more accurate analysis. A non-limiting examplemethod of cleaning up the HF signal is described in above-mentioned U.S.Pat. No. 8,626,275.

In some embodiments the high frequency electrogram signals areoptionally aligned based on one or more of the following:

-   -   a time of depolarization onset of the heart as detected in an        electrogram, optionally an electrogram picked up by an electrode        in the heart, preferably in the right atrium; and    -   a time of pacing by a pacemaker in the Right Atrium (RA), Right        Ventricle (RV) or Left Ventricle (LV).

Reference is now additionally made to FIGS. 2H and 2I, which are graphs710 720 showing good correlation and bad correlation of HF signals 714715 716 724 725 726 according to an example embodiment of the invention.

FIG. 2H depicts the graph 710 of the HF signals 714 715 716 showing theHF signals 714 715 716 having a relatively good correlation with eachother.

FIG. 2I depicts the graph 720 of the HF signals 724 725 726 having arelatively worse correlation with each other.

It is additionally noted that the graphs 710 720 have a Y-axis 711 ofarbitrary correlation units, and an X-axis 712 of time in milliseconds.

FIGS. 2H and 21 illustrate that HF signals may be aligned with eachother, optionally by shifting the HF signal in time forward and backwardto achieve an optional correlation, and/or a correlation coefficientvalue which is above a specific correlation coefficient threshold. Anon-limiting example of such a specific correlation coefficientthreshold is optionally 0.7, or 70%, and a range of 0.5 (50%) to 0.95(95%) is a range contemplated for such values

In some embodiments, measuring correlation between HF electrogramsignals is optionally used to detect noisy HF signals, and optionally todisregard the noisy signals.

In some embodiments, the alignment may optionally be performed based onaligning low-frequency electrogram signals.

Reference is now additionally made to FIG. 2J, which depicts graphs771-986 of HF signals of 16 different QRS complexes according to anexample embodiment of the invention.

The graphs 771-986 depict HF signals of consecutive QRS complexes,depicting some signals which appear clean and lend themselves well to becorrelated to each other, and some which appear noisier and are not sowell correlated to each other.

In some embodiments, performing correlation between two electrogramsignals which have been sampled for different heartbeats is optionallyperformed by performing a mathematical correlation function between twovectors which contain sample values of amplitudes of the two electrogramsignals. A result of the correlation is a correlation coefficient.

In some embodiments correlation is performed at different time-shiftsbetween the two vectors, and a maximum value of the correlationcoefficient is optionally determined.

In some embodiments, a time-shift corresponding to the maximum value isdetermined to be a time-shift desired for aligning the two electrogramsignals.

Reference is now additionally made to FIG. 2K, which depicts a graph 820of alignment of an unfiltered electrogram signal 826 to a template 824according to an example embodiment of the invention.

The graph 820 depicts an electrogram signal 826 and an inherentelectrogram signal which acts as a template 824 for a QRS complex of aheartbeat, both without filtering for HF frequencies. The electrogramsignal 826 and the template 824 have a shape like a familiarlow-frequency QRS complex signal because low frequency components of anelectrogram signal typically have a much larger amplitude than highfrequency components of the electrogram signal.

The graph 820 has a Y-axis 822 of voltage in microvolt units, and anX-axis 821 of time in milliseconds.

FIG. 2K depicts an inherent shape of the electrogram signal as portrayedby the template 824.

In some embodiments, an unfiltered electrogram signal such as theunfiltered electrogram signal 826 is optionally used to alignelectrogram signals, including HF signals, that is, to determine a timeshift between electrogram signals from different heartbeats, so as tocompare the electrogram signals to each other and/or to a baseline.

In some embodiments, a filtered low-frequency electrogram signal (notshown) is optionally used to align the electrogram signals.

In some embodiments, the alignment is based on one of the alignmentmethods described above, and it is a high-frequency components of theelectrogram signals which are then compared to each other and/or to abaseline.

In some embodiments the QRS complex template 824 is optionally producedby curve fitting a mathematical function to an inherent electrogramsignal or to a QRS complex section of an inherent electrogram signal.The inherent QRS complex signal is optionally an exemplary QRS complexsignal, optionally produced from one or more unfiltered, orlow-frequency electrogram signals or QRS complex sections of suchelectrogram signals.

In some embodiments, an inherent HF signal is calculated. Such aninherent HF signal is depicted in FIG. 2L, and described below.

In some embodiments the curve fitting optionally involves calculating anumber of coefficients for the mathematical function to fit the inherentHF signal.

In some embodiments the mathematical function is a polynomial function.

In some embodiments the mathematical function is for example cubicspline.

In some embodiments the number of coefficients for producing thetemplate 824 is typically 20 or more, or between 5 and 30, and even arange of 3, 5, 10, 20, 50 or 100 coefficients are contemplated.

In some embodiments the QRS complex template 824 is optionally producedby averaging a number of electrogram signals, by way of a non-limitingexample such as the electrogram signal 826, over several heartbeats.

Reference is now additionally made to FIG. 2L, which is a graph 800depicting an HF portion of an inherent electrogram signal 806 and anactual HF signal 804, according to an example embodiment of theinvention.

The HF portion of an electrogram signal, including both the inherentelectrogram signal 806 and the actual HF signal 804 is potentially lessdependent on noise originating from a patient's movement, andpotentially supports better detection and/or monitoring of a patient'sheart condition.

FIG. 2L depicts the HF portion of the inherent electrogram signal 806,and the actual HF signal 804, either of which can be compared to abaseline (not shown) and potentially detect changes in a patient'sphysiological condition.

The graph 800 has a Y-axis 802 of millivolt units, and a X-axis 732 oftime in milliseconds.

In some embodiments analysis of the high frequency signal is optionallyfiltered for a frequency above 500 Hz.

Noise

In some embodiments, a heartbeat period which produces a noisyelectrogram signal is discarded from use in the analysis.

In some embodiments determining that an electrogram signal is noisy isoptionally performed based on a high-frequency-filtered electrogramsignal. In some embodiments determining that an electrogram signal isnoisy is optionally performed based on a low-frequency-filteredelectrogram signal. In some embodiments determining that an electrogramsignal is noisy is optionally performed based on an electrogram signalwhich includes both high and low frequencies.

In some embodiments, detecting a noisy HF electrogram signal isoptionally performed by measuring noise in a quiet segment of an HFelectrogram signal, such as in an ST segment, and/or between a T segmentand a following P segment, and/or in a T segment, and/or simply outsideof a QRS complex segment.

In some embodiments, detecting a noisy HF electrogram signal isoptionally performed by calculating a correlation coefficient of theelectrogram signal to an inherent electrogram signal, and comparing thecorrelation coefficient to a threshold value.

In some embodiments, a threshold level for determining that a HFelectrogram signal is noisy is measuring noise, by way of a non-limitingexample RMS noise of less than 1 microvolt. In some embodiments, the RMSnoise threshold for the HF signal is optionally between 0.2 microvoltsand 2 microvolts.

In some embodiments, upon detecting an electrogram signal having a noisevalue greater than the noise threshold, the signal is discarded from usefor any purpose. In some embodiments, the noisy signal is discarded fromuse in determining a patient's condition. In some embodiments, a noisysignal is tagged as noisy, and saved associated with the tag.

The Breathing cycle

The terms breathing cycle portion and breathing cycle segment are usedinterchangeably in the specification and claims.

A linkage between a breathing cycle and heart rate is known in theliterature and referred to as Respiratory Arrhythmia. The heart rate, inturn, is among the factors which govern the behavior of the highfrequency ECG signal, which results in a potential coupling betweenanalysis of high frequency ECG signals parameters and the breathingcycle.

In some embodiments the breathing cycle is optionally analyzed andcomparison of high frequency ECG analysis results is optionally donebetween measurements taken at similar times in the breathing cycle. Forexample, a comparison of high frequency ECG parameters is performedbetween high frequency ECG parameters measured at maximum exhalation.

Reference is now made to FIG. 3, which is a simplified prior artillustration of effects of breathing on electrocardiogram signals.

FIG. 3 depicts a graph 300 of respiration-induced modulation of QRScomplex amplitude in a regular ECG signal. An upper trace 302 depicts anECG trace, and a lower trace 304 depicts respiration as measured by apneumatic respiration transducer (PRT) placed around a chest of asubject. The upper trace 302 and the lower trace 304 depict measurementsover a duration of 10 seconds. The graph 300 is taken from theabove-mentioned article titled “Derivation of Respiratory Signals fromMulti-lead ECGs” by Moody et al.

FIG. 3 depicts and the article teaches a method for analyzing QRScomplex amplitude in a regular ECG signal and respiratory actions. Byway of a non-limiting example, the amplitude of the QRS complex is seento increase and decrease in relation to the respiration.

In some embodiments, high frequency ECG parameters are measured onlyduring a specific portion of a breathing cycle, by way of somenon-limiting examples, when QRS complex amplitude is maximal or when QRScomplex amplitude is minimal.

In some embodiments detecting the segment of the breathing cycleincludes measuring amplitude of a QRS complex of a low frequencyelectrogram.

In some embodiments, high frequency ECG parameters are measured onlyduring a specific portion of a breathing cycle, by way of somenon-limiting examples, when the cardiac cycle is shorter than average orwhen the cardiac cycle is longer than average.

In some embodiments detecting the segment of the breathing cyclecomprises measuring a duration of a cardiac cycle.

In some embodiments, high frequency ECG parameters are measured onlyonce during a breathing cycle instead of every heartbeat. Suchembodiments provide a method of potentially saving power.

In some embodiments the stages of the breathing are optionally measuredby one or more motion sensors in or connected to the implanted device.

In some embodiments the stages of the breathing are optionally measuredby a strap around the chest. In such embodiments the strap is optionallycommunicating with an analysis unit, optionally an external analysisunit using electrodes with a body, such as inserted via a catheter.

In some embodiments the stages of the breathing are optionally measuredby an audio sensor. Such detection by audio sensors can potentiallyoperate both in implantable devices and in external devices.

In some embodiments the stages of the breathing are optionally measuredby a spirometric device. A spirometric device may be in a unit externalto a subject's body, sending a signal to an implanted unit to enabledetecting the stages of the breathing.

In some embodiments, use of the stages of breathing during HF signalanalysis is enabled when a signal from the spirometric device isreceived by the implanted device. In some embodiments, the stages ofbreathing are not used during HF signal measurements when a signal fromthe spirometric device is not received by the implanted device.

In some embodiments, detecting a portion of the breathing cycle isoptionally performed by using motion sensors and analysis to detectcyclic movement of a subject's chest.

In some embodiments, the specific stages of the breathing cycle areoptionally selected based on characterization of electrogram based onlow frequency features such as amplitude of the QRS complex and/or atime within a cardiac cycle.

Additional Physiological Sensors

Using state-of-the-art physiological sensors such as, by way of anon-limiting example, a bioimpedance sensor such as Optivol byMedtronic, it is possible to measure physiological parameters, such as,by way of a non-limiting example, blood pressure in various loci, forexample, in the pulmonary arteries. Additional non-limiting examples ofphysiological sensors include implantable hemodynamic monitoring usingthe Chronicle IHM system by Medtronic and the pressure monitor namedheartPOD by St Jude Medical. Such measurements provide a potentiallymore accurate description of a subject's status, and potentiallycorrelate to the High frequency ECG results as well as to otherparameters relating to a given physiological conditions.

The High frequency ECG parameters may potentially have naturalvariations, even under normal circumstances. Gating or triggering ananalysis of the HF signal based on values of physiological parameterssuch as blood pressure, pulse and breathing cycle, potentially renderthe High frequency ECG analysis more sensitive and accurate, increasingits usefulness for the indication of ischemic states and ischemicdisease.

Simultaneous acquisition, and/or registration and/or analysis of Highfrequency ECG and additional variables (such as blood pressure, Heartrhythm and rate, ST changes, T-wave abnormalities, late potentials,T-wave alternans, etc.) potentially provide at least the following twoconsequences. First, the High frequency ECG is optionally analyzed andevaluated with respect to a multi-parameter state when recording aperson's baseline. Second, High frequency ECG measurements areoptionally made or analyzed only at certain, possibly predetermined,multi-parameter states.

In some embodiments the system also includes means for measuring andanalyzing a low frequency electrogram signal. Low frequency electrogramanalysis optionally includes analysis of: heart rate, ST segmentchanges, heart rate variability, T wave abnormalities including T-waveinversion and T-wave alternans; and QT interval.

In some embodiments, specific categories are defined, each categoryincluding a range of values for variables. The variables include resultsof analysis, such as values of HF electrogram analysis indexes andvalues of low frequency electrogram analysis; and values ofphysiological measurements, such as blood pressure, heart rhythm andrate, ST changes, T-wave abnormalities, T-wave alternans, etc.

In some embodiments a medical pathological condition is optionallydetected when there is a consistent change in both High frequencyelectrogram indexes and other parameters such ST changes in a regularECG trace, and/or a change in heart rate. When a correlation between theHF electrogram indexes and the other parameters appears more than aspecific number of times in a row this is optionally an indication forischemia. In some embodiments, when more than one, two, 5 or 10 suchcorrelations appear per day an alert is produced.

In some embodiments, determining a baseline for use in a latercomparison, in order to detect ischemia, is optionally done bycontinuous measurements and constant updating.

In some embodiments ischemia is detected by reaching specific highfrequency ECG values. By way of example when changes in RMS values ofthe high frequency ECG are greater than 5%, 10%, 20%, 30%, 40%, or 50%of a reference RMS value.

In some embodiments, for a morphological index as described inabove-mentioned U.S. Pat. No. 8,626,275, a change in the morphologicalindex greater than 2%, 4%, 5%, 7%, 10%, or 15% of a referencemorphological index value optionally indicates possible ischemia.

In various embodiments, reference values, also termed baseline values,are determined by various methods. Some non-limiting example methodsinclude:

using a historical average value which was measured over a previous day,week, month or year. In some embodiments the historical average isoptionally selected so as to be sensitive to heart rate and optionallyto additional physiological conditions; and

using a baseline value which was measured at one time during a setupperiod or a set up test.

In some embodiments the baseline value is optionally measured undersimilar conditions, such as similar heart rate (pulse) and/or similarbreathing rate and/or a similar portion of a cardiac cycle and/or asimilar portion of a breathing cycle.

In some embodiments acute ischemia is detected by detecting changescompared to the baseline.

In some embodiments the baseline value changes over time—e.g. a baselinemeasured and calculated for a window of N consecutive heartbeats onceevery M heartbeats, and/or every period of time such as several times anhour, a day, a week, a month.

In some embodiments acute ischemia is detected by detecting changes inHF electrogram parameters measured at a low heart rate period and at ahigher heart rate period. In some embodiments that change in heart ratebetween the two periods is greater than 10%, 20%, 40%, 50%, 100%.

In some embodiments the change in heart rate is optionally in term of astandard deviation relative to an average and standard deviation of apopulation of N heartbeats.

In some embodiments, by tracking the physiological and High frequencyECG parameters of the baseline itself a slow deterioration in asubject's condition is optionally detected.

In some embodiments, the High frequency ECG parameters are used for adifferential diagnosis between ventricular tachycardia (VT) andsupraventricular tachycardia (SVT). During VT a morphological indexand/or amplitude of the HF signal changes from beat to beat, while inSVT a change from beat to beat is typically not significant.

In some embodiments, trends of calculated values are calculated and/orstored and/or transmitted. The calculated values include, by way of somenon-limiting example, regular ECG values, HF electrogram values, valuesas described in U.S. Pat. No. 8,626,275, and so on.

In some embodiments, correlations between calculated values arecalculated and/or stored and/or transmitted.

Intracoronary Electrodes

In some embodiments, one or more intracoronary electrodes are used foracquisition of the electrogram.

In some embodiments, the intracoronary electrodes are optionally locatednear to a known and/or to a suspected partial or complete occlusion inan artery. The electrogram signal is optionally measured proximally anddistally from the occlusion, and High frequency ECG values of the signalare optionally compared to examine differences in the electricalcharacteristics of the tissues proximal and distal to the occlusion. Thedifferences potentially indicate changes in vitality and potentiallyindicate an ischemic condition. By way of a non-limiting example, achange in HF indexes between a point before blockage and a point afterthe blockage change significantly. A change in RMS HF values of greaterthan 5%, 10%, 20%, 30%, 40%, or 50% of a reference HF RMS value and/or achange in a morphological index by more than 1%, 2%, 3%, 4%, 5% or 6% ofa reference morphological index.

Reference is now made to FIG. 4A, which is a simplified illustration ofelectrodes for picking up an electrogram within a blood vessel accordingto an example embodiment of the invention.

FIG. 4A depicts an example blood vessel, an artery 402. The artery 402has, for example, a blockage 404. A first electrode 406 having a bipolarpickup 407 is inserted up until beyond the blockage 404. A secondelectrode 408 having a bipolar pickup 409 is inserted until before theblockage 404.

In some embodiments one or both of the electrodes 406 408 may bemonopolar electrodes (not shown) or multipolar electrodes (not shown).

In some embodiments there is a use of single electrode configurationwhich measures the electrogram at both locations: before and beyond theblockage 404.

Reference is now made to FIG. 4B, which is a simplified illustration ofelectrodes for picking up an electrogram within a blood vessel accordingto an example embodiment of the invention.

FIG. 4B depicts an example blood vessel, an artery 402. The artery 402has, for example, a blockage 404. A first electrode 416 having a bipolarpickup 417 is inserted up until beyond the blockage 404. The firstelectrode 416 also includes an electronics unit 422, which optionallycommunicates wirelessly with an external analyzer 424, transmitting asignal corresponding to an HF signal picked up by the bipolar pickup417.

A second electrode 418 having a bipolar pickup 419 is inserted untilbefore the blockage 404. The second electrode 418 also includes anelectronics unit 420, which optionally communicates wirelessly with theexternal analyzer 424, transmitting a signal corresponding to an HFsignal picked up by the bipolar pickup 419. In some embodiments one orboth of the electrodes 416 418 may be monopolar electrodes (not shown)or multipolar electrodes (not shown).

In some embodiments there is a use of single electrode configurationwhich measures the electrogram at both locations: before and beyond theblockage 404, at different times.

In some embodiments High frequency ECG measurement by intracoronaryelectrodes potentially assists in determining whether stent placement isrecommended.

A change in RMS HF values of greater than 5%, 10%, 20%, 30%, 40%, or 50%of a reference HF RMS value, and/or a change in a morphological index bymore than 1%, 2%, 3%, 4%, 5% or 6% of a reference morphological indexoptionally assist in determining whether stent placement is recommended.

In some embodiments High frequency ECG measurement by intracoronaryelectrodes is optionally combined with FFR (fractional flow reserve)analysis and also potentially assists in determining whether stentplacement is recommended.

FFR analysis typically measures local pressure in a blood vessel. If thepressure drops below a set pressure the drop is an indication that theremight be a benefit for inserting a stent. The FFR method typicallyevaluates whether there is a collateral blood supply or whether tissueis necrotic due to lack of blood circulation.

The above-mentioned determinations of coronary vessel condition and/ortreatment may be performed both by implantable electrodes and byelectrodes temporarily inserted by catheter.

The above-mentioned determinations of coronary vessel condition arepotentially useful for post-revascularization evaluation of therevascularization efficacy.

In some embodiments, the coronary blood vessel in which the electrogramis measured with relation to the occlusion is a coronary artery. In someembodiments, the coronary blood vessel the coronary blood vessel is acoronary vein. In some embodiments the coronary blood vessel is thecoronary sinus.

In some embodiments detection of ischemia onset is performed based on achange in one or more of the following parameters of the HF signal of anelectrogram over at least one intracardiac electrode:

an RMS level of the HF signal of the electrogram;

a function of the RMS levels of the HF signal of the electrogram indifferent portions of the cardiac cycle, such as, for example, a P or aT portion of the cardiac cycle;

an envelope maximum of the high frequency signal of the electrogram;

a function of the envelope levels in different portions of the cardiaccycle, of the high frequency signal of an electrogram;

an envelope width of the high frequency signal of an electrogram, asdescribed in above-mentioned U.S. Pat. No. 8,626,275;

an area of a reduced amplitude zone (RAZ) of the electrogram HF signal,as described in above-mentioned mentioned U.S. Pat. No. 8,626,275; and

an area of a RAZ in the envelope of the electrogram HF Signal, asdescribed in above-mentioned mentioned U.S. Pat. No. 8,626,275.

In some embodiments warning is provided of potential onset of anischemic event, optionally based on a significant reduction in the HFintensity during an increase in heart rate. Optionally, reduction levelsare adjusted for individual patients, and are typically 50% reductionduring a heart rate increase of 30%, and/or when a patient traverses 70%of the patient's maximal heart rate. A potential scenario includes thepatient experiencing a significant reduction in the HF content everytime the patient has a significant heart rate increase.

In some embodiments when a system detects a repeating pattern the systemincreases a confidence value to produce an alert.

In some embodiments the alert optionally produces a sound alert for thepatient and/or sends a message to medical personnel tracking thepatient.

In some embodiments sound is produced by using a simple sound generatorbuilt into the device. In some embodiments the alert is produced byvibration of the device.

In some embodiments, for communication purposes, an implantable deviceincludes a communication module. In some embodiments the communicationmodule optionally transmits information through a receiving station,which in some cases optionally includes a smart phone, to a medicalprofessional center.

In some embodiments a HF portion of an electrogram is measured using atleast one intracardiac electrode.

In some embodiments the following configurations are optionally used formeasuring an intracardiac electrogram HF signal: a single monopolarelectrode that measures a signal between an intracardiac electrode and acan (container) of an implantable device;

a bipolar electrode;

two intracardiac electrodes placed at different places within the heart;

one intracardiac and one epicardiac electrode; and

two epicardiac electrodes.

In some embodiments a bipolar electrode, also termed a lead, isoptionally used, having two electrical pickup points, which may also betermed two electrodes. In some embodiments the distance between the twoelectrical pickup points is 1-3 millimeters, or 1-5 millimeters, or 1-7millimeters or 1-10 millimeters, which potentially measure a localchange in an electrogram, potentially measuring a difference in theelectrogram between the two adjacent electrical pickup points.

In some embodiments detection of ischemia and/or of onset of ischemia isoptionally based, at least in part, on a function of RMS values of anelectrogram HF signal, optionally measured using one of theabove-mentioned electrode configurations.

In some embodiments detection of ischemia and/or of onset of ischemia isoptionally based, at least in part, on a comparison of RMS values of anelectrogram HF signal, optionally at different instances of similarheart rate values, such as, for example:

a difference between the RMS values exceeding a threshold differencevalue; and

a ratio between the RMS values exceeding a threshold ratio value.

In some embodiments detection and differentiation between ventriculartachycardia and supraventricular tachycardia is optionally based, atleast in part, on a function of RMS values of electrogram HF signal,using one of the above-mentioned electrode configurations.

In some embodiments differentiating between ventricular tachycardia andsupraventricular tachycardia is optionally based, at least in part, on acomparison of RMS values of electrogram HF signal at different instancesof similar heart rate values. The difference and/or the ratio of the RMSvalues measured, using one of the above-mentioned electrodeconfigurations, are optionally considered for the differentiation.

By way of a non-limiting example, if at different time periods whichhave an approximately similar high heart rate there is a significantdifference in a HF RMS value, the difference potentially indicatesexistence of tachycardia originating from the ventricle (VT), asdescribed above.

In some embodiments acquisition of the high frequency electrogram signalis performed using intracoronary monopolar and/or bipolar electrodes inone or more locations relative to a complete and/or partial occlusionand/or suspected occlusion of a coronary artery. In some embodiments,the HF electrogram signal proximally and distally from an occlusion isoptionally acquired and optionally compared. In some embodiments, one ormore of the following parameters is optionally compared between aproximal and a distal HF electrogram signal:

a difference between RMS values at the proximal and distal locations;

a ratio between the RMS values at the proximal and distal locations; and

a function of numerical characteristics of the HF signal envelopes atthe proximal and distal locations.

In some embodiments detection of a difference in ischemic conditionand/or vitality between two locations near a complete or partialocclusion of a coronary artery is optionally based, at least in part, onthe methods and apparatus described above.

In some embodiments detection of difference in ischemic condition and/orvitality between two electrode locations near a complete or partialocclusion of a coronary artery is optionally based, at least in part, onthe methods and apparatus described above, optionally also combined withresults from FFR (fractional flow reserve) analysis.

In some embodiments detection of difference in ischemic condition and/orvitality between two locations near a complete or partial occlusion of acoronary artery is optionally based on the methods and apparatusdescribed above, optionally for assisting in determining whether stenttherapy is needed. In some embodiments detection of difference inischemic condition and/or vitality between two electrode locations neara complete or partial occlusion of a coronary artery is optionallybased, at least in part, on the methods and apparatus described above,optionally for post-revascularization assessment of revascularizationresults and current ischemic condition.

Reference is now made to FIG. 5, which is a flow chart of a method foranalyzing a high frequency (HF) electrogram signal according to anexample embodiment of the invention.

The example embodiment depicted in FIG. 5 includes:

providing at least one electrogram signal from an electrode locatedwithin a subject's body (505);

sampling the electrogram signal at a high frequency, generating a highfrequency (HF) electrogram signal (510);

having a computer measure at least one time-varying parameter of the HFelectrogram signal (515);

having a computer detect a change in the time-varying parameter incomparison to a baseline value of the time-varying parameter (520);

having the computer generate an alert based, at least in part, on thedetection (525).

Reference is now made to FIG. 6, which is a flow chart of a method foranalyzing a high frequency (HF) electrogram signal according to anexample embodiment of the invention.

The example embodiment depicted in FIG. 6 includes:

providing a first electrogram signal from a first location of anintracoronary electrode adjacent to an occlusion of a coronary bloodvessel (605);

sampling the first electrogram signal at a high frequency, generating afirst high frequency (HF) electrogram signal (610);

providing a second electrogram signal from a second location of anintracoronary electrode adjacent to the occlusion of the coronary bloodvessel (615);

sampling the second electrogram signal at a high frequency, generating asecond high frequency (HF) electrogram signal (620);

having a computer measure at least one parameter of the first HFelectrogram signal and the second HF electrogram signal (625); and

having the computer compare the at least one parameter of the first HFelectrogram signal and the second HF electrogram signal and produce aresult of the comparison (630).

In some embodiments, the coronary blood vessel is a coronary artery.

In some embodiments, the coronary blood vessel is a coronary vein, byway of a non-limiting example the coronary sinus.

Reference is now made to FIG. 7A, which is a flow chart of a method foranalyzing a high frequency (HF) electrogram signal according to anexample embodiment of the invention.

The example embodiment depicted in FIG. 7A includes:

(a) providing at least one electrogram signal from an electrode locatedwithin a subject's body (905);

(b) measuring the electrogram signal at a high frequency only during aspecific segment of a cardiac cycle, generating a HF electrogram signalfor the specific segment of the cardiac cycle (910); and

(c) calculating at least one time-varying parameter of the generated HFelectrogram signal (915),

in which the specific segment of the cardiac cycle is a one of a groupconsisting of: a P segment; a Q segment; a R segment; a S segment; a Tsegment; and a QRS complex.

Reference is now made to FIG. 7B, which is a flow chart of a method foranalyzing a high frequency (HF) electrogram signal according to anexample embodiment of the invention.

The example embodiment depicted in FIG. 7B includes:

(a) providing at least one electrogram signal from an electrode locatedwithin a subject's body (955);

(b) measuring the electrogram signal at a high frequency only during aspecific segment of a breathing cycle, generating a HF electrogramsignal for the specific segment of the breathing cycle (960); and

(c) having a computer measure at least one time-varying parameter of theHF electrogram signal (970).

It is expected that during the life of a patent maturing from thisapplication many relevant electrogram acquisition techniques will bedeveloped and the scope of the term electrogram is intended to includeelectrograms acquired by all such new technologies a priori.

It is expected that during the life of a patent maturing from thisapplication many relevant wireless transmission techniques will bedeveloped and the scope of the term wireless transmission is intended toinclude wireless transmission performed by all such new technologies apriori.

It is expected that during the life of a patent maturing from thisapplication many relevant implantable electrodes will be developed andthe scope of the term implantable electrodes is intended to include allsuch new technologies a priori.

As used herein the term “about” refers to ±10%.

The terms “comprising”, “including”, “having” and their conjugates mean“including but not limited to”.

The term “consisting of” is intended to mean “including and limited to”.

The term “consisting essentially of” means that the composition, methodor structure may include additional ingredients, steps and/or parts, butonly if the additional ingredients, steps and/or parts do not materiallyalter the basic and novel characteristics of the claimed composition,method or structure.

As used herein, the singular form “a”, “an” and “the” include pluralreferences unless the context clearly dictates otherwise. For example,the term “a unit” or “at least one unit” may include a plurality ofunits, including combinations thereof.

The words “example” and “exemplary” are used herein to mean “serving asan example, instance or illustration”. Any embodiment described as an“example or “exemplary” is not necessarily to be construed as preferredor advantageous over other embodiments and/or to exclude theincorporation of features from other embodiments.

The word “optionally” is used herein to mean “is provided in someembodiments and not provided in other embodiments”. Any particularembodiment of the invention may include a plurality of “optional”features unless such features conflict.

Throughout this application, various embodiments of this invention maybe presented in a range format. It should be understood that thedescription in range format is merely for convenience and brevity andshould not be construed as an inflexible limitation on the scope of theinvention. Accordingly, the description of a range should be consideredto have specifically disclosed all the possible sub-ranges as well asindividual numerical values within that range. For example, descriptionof a range such as from 1 to 6 should be considered to have specificallydisclosed sub-ranges such as from 1 to 3, from 1 to 4, from 1 to 5, from2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numberswithin that range, for example, 1, 2, 3, 4, 5, and 6. This appliesregardless of the breadth of the range.

Whenever a numerical range is indicated herein, it is meant to includeany cited numeral (fractional or integral) within the indicated range.The phrases “ranging/ranges between” a first indicate number and asecond indicate number and “ranging/ranges from” a first indicate number“to” a second indicate number are used herein interchangeably and aremeant to include the first and second indicated numbers and all thefractional and integral numerals therebetween.

As used herein the term “method” refers to manners, means, techniquesand procedures for accomplishing a given task including, but not limitedto, those manners, means, techniques and procedures either known to, orreadily developed from known manners, means, techniques and proceduresby practitioners of the chemical, pharmacological, biological,biochemical and medical arts.

It is appreciated that certain features of the invention, which are, forclarity, described in the context of separate embodiments, may also beprovided in combination in a single embodiment. Conversely, variousfeatures of the invention, which are, for brevity, described in thecontext of a single embodiment, may also be provided separately or inany suitable sub-combination or as suitable in any other describedembodiment of the invention. Certain features described in the contextof various embodiments are not to be considered essential features ofthose embodiments, unless the embodiment is inoperative without thoseelements.

Although the invention has been described in conjunction with specificembodiments thereof, it is evident that many alternatives, modificationsand variations will be apparent to those skilled in the art.Accordingly, it is intended to embrace all such alternatives,modifications and variations that fall within the spirit and broad scopeof the appended claims.

All publications, patents and patent applications mentioned in thisspecification are herein incorporated in their entirety by referenceinto the specification, to the same extent as if each individualpublication, patent or patent application was specifically andindividually indicated to be incorporated herein by reference. Inaddition, citation or identification of any reference in thisapplication shall not be construed as an admission that such referenceis available as prior art to the present invention. To the extent thatsection headings are used, they should not be construed as necessarilylimiting.

What is claimed is:
 1. An implantable device for analyzing a highfrequency (HF) electrogram signal comprising: an implantable electrodefor use inside a living body; a signal pickup configured to pick up anelectrogram signal comprising a high frequency (HF) component; a signalfilter connected to the signal pickup and configured to measure a highfrequency (HF) component from the electrogram signal only during aspecific portion of a cardiac cycle; and an analyzer for analyzing theHF component of the electrogram signal, wherein: the signal pickup, thesignal filter and the analyzer are comprised within an implantablecontainer; and the analyzer is configured to analyze at least onetime-varying parameter of the HF component of the electrogram signal;and the signal filter is configured to measure said electrogram signalby using a signal picked up from at least one electrode selected from agroup consisting of: (a) an intracardiac electrode; (b) a subcutaneouselectrode; (c) a can of said implanted device; (d) a combination of twoof the above.
 2. The device of claim 1 in which the specific portion ofthe cardiac cycle comprises at least part of a specific segment of thecardiac cycle, the specific segment of the cardiac cycle being one of agroup consisting of: a P segment; a Q segment; a R segment; a S segment;a T segment; and a QRS complex segment.
 3. The device of claim 1 inwhich said signal filter is arranged to start measuring said electrogramsignal a specific period of time following a synchronizing pacingsignal.
 4. The device of claim 1 in which the analyzer is configured todetect a change in the time-varying parameter in comparison to abaseline value of the time-varying parameter.
 5. The device of claim 1in which: the specific segment of the cardiac cycle is a P segment; andthe analyzer is configured to provide indication of atrial arrhythmia,and further comprising a pacing unit for manipulating a pacing rate,based on the indication, to overcome the atrial arrhythmia.
 6. Thedevice of claim 1 in which: the specific segment of the cardiac cycle isa QRS complex; and the analyzer is configured to provide indication ofonset of an ischemic event, and further comprising a pacing unitarranged to manipulate a pacing rate, based on the indication, toovercome the onset of the ischemic event by reducing the pacing rate. 7.A method for analyzing a high frequency (HF) electrogram signalcomprising: (a) providing at least one electrogram signal from anelectrode located within a subject's body; (b) measuring the electrogramsignal at a high frequency only during a specific portion of a cardiaccycle, generating a HF electrogram signal for the specific portion ofthe cardiac cycle; and (c) calculating at least one time-varyingparameter of the generated HF electrogram signal, wherein the specificportion of the cardiac cycle comprises at least part of a specificsegment of the cardiac cycle, the specific segment of the cardiac cyclebeing one of a group consisting of: a P segment; a Q segment; a Rsegment; a S segment; a T segment; and a QRS complex segment.
 8. Themethod of claim 7 in which the providing at least one electrogram signalfrom an electrode located within a subject's body comprises measuring anelectrogram signal by using at least one electrode selected from a groupconsisting of: (a) an intracardiac electrode; (b) a subcutaneouselectrode; (c) a can of an implanted device; (d) a combination of two ofthe above.
 9. The method of claim 7 in which the specific segment of thecardiac cycle is a P segment, and the analysis is used to providewarning of a condition selected from a group consisting of: an irregularpropagation of an action potential in a cardiac atria; atrialtachycardia; atrial bradycardia; and atrial arrhythmia.
 10. The methodof claim 7 in which: the specific segment of the cardiac cycle is a Psegment; and the analysis is used to provide warning of atrialarrhythmia, and further comprising manipulating a pacing rate toovercome the atrial arrhythmia.
 11. The method of claim 7 in which thespecific segment of the cardiac cycle comprises a QRS complex, and theanalysis is used to provide warning of onset of an ischemic event. 12.The method of claim 11 in which the analysis comprises detection of areduction in amplitude of the HF electrogram signal.
 13. The method ofclaim 7 in which the sampling of the electrogram signal at a highfrequency comprises sampling the electrogram signal at a high frequencyduring a specific segment of a breathing cycle.
 14. The method of claim7 and further comprising aligning and averaging a plurality of HFelectrogram signals in which the aligning comprises synchronization ofHF electrogram signals based on a pacing signal.
 15. The method of claim7 and further comprising comparing a value of the time-varying parameterof the HF electrogram signal and a baseline value of the time-varyingparameter of the HF electrogram signal.
 16. The method of claim 7 andfurther comprising comparing a value of the time-varying parameter ofthe HF electrogram signal and a prior value of the of the time-varyingparameter of the HF electrogram signal under same heart rate conditions.17. The method of claim 16 in which the same conditions are selectedfrom a group consisting of: (a) same heart rate; (b) same heart rateincrease; (c) same heart rate decrease; (d) same pattern of change ofheart rate.
 18. The method of claim 7 and further comprising comparing acurrent value of the time-varying parameter of the HF electrogram signaland a prior value of the of the time-varying parameter of the HFelectrogram signal in which the prior value was measured for a heartrate different by a pre set amount from a heart rate at which the priorvalue was measured.
 19. An implantable device for analyzing a highfrequency (HF) electrogram signal comprising: an implantable electrodefor use inside a living body; a signal pickup configured to pick up anelectrogram signal comprising a high frequency (HF) component; ameasurement unit for measuring a high frequency (HF) component of theelectrogram signal only during a specific segment of a breathing cycle;and an analyzer for analyzing the HF component of the electrogramsignal, wherein: the signal pickup, the measurement unit and theanalyzer are comprised within an implantable container; the analyzer isconfigured to analyze at least one time-varying parameter of the HFcomponent of the electrogram signal; and the analyzer is configured todetermine the specific segment of the breathing cycle.
 20. A method foranalyzing a high frequency (HF) electrogram signal comprising: (a)providing at least one electrogram signal from an electrode locatedwithin a subject's body; (b) measuring the electrogram signal at a highfrequency only during a specific segment of a breathing cycle,generating a HF electrogram signal for the specific segment of thebreathing cycle; and (c) having a computer measure at least onetime-varying parameter of the HF electrogram signal.